Solution Navier-Stocks Equations of the Blood as a Non-Newtonian Fluid in the Left Ventricle

ABSTRACT

The present invention discloses a method for solving Navier-Stokes equation of the blood dynamic as a Non-Newtonian fluid in the left ventricle is a serious problem where is strongly related to a good modeling of the myocardial motion as an elastic membrane. At this invention we design a new software which studies the blood flow inside a biological membrane where is estimated by quadratic forms that their algebraic equations have separately been investigated by a software which can be taken as a reference at this invention.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims the benefit of U.S. provisional patent applications Ser. No. 61/345,615, filed May 18, 2010; 61/434,970 filed on Jan. 21, 2011; and 61/434,979 filed on Jan. 21, 2011, which are incorporated herein by reference in their entireties.

FIELD OF INVENTION

The present invention relates to a method for studying blood flow regionally near echocardiography samples and globally inside the left ventricle and software and system thereof.

BACKGROUND OF INVENTION

The Navier-Stokes equations, named after Claude-Louis Navier and George Gabriel Stokes, describe the motion of fluid substances. These equations arise from applying Newton's second law to fluid motion, together with the assumption that the fluid stress is the sum of a diffusing viscous term (proportional to the gradient of velocity), plus a pressure term.

The equations are useful because they describe the physics of many things of academic and economic interest. They may be used to model the weather, ocean currents, water flow in a pipe and air flow around a wing. The Navier-Stokes equations in their full and simplified forms help with the design of aircraft and cars, the study of blood flow, the design of power stations, the analysis of pollution, and many other things. Coupled with Maxwell's equations they can be used to model and study magneto-hydrodynamics.

Together with supplemental equations (for example, conservation of mass) and well formulated boundary conditions, the Navier-Stokes equations seem to model fluid motion accurately; even turbulent flows seem (on average) to agree with real world observations.

The Navier-Stokes equations assume that the fluid being studied is a continuum not moving at relativistic velocities. At very small scales or under extreme conditions, real fluids made out of discrete molecules will produce results different from the continuous fluids modelled by the Navier-Stokes equations. Depending on the Knudsen number of the problem, statistical mechanics or possibly even molecular dynamics may be a more appropriate approach.

Time tested formulations exist for common fluid families, but the application of the Navier-Stokes equations to less common families tends to result in very complicated formulations which are an area of current research. For this reason, these equations are usually written for Newtonian fluids. Studying such fluids is “simple” because the viscosity model ends up being linear; truly general models for the flow of other kinds of fluids, such as blood as of 2011, do not exist.

Solving the Navier-Stocks equations for an arbitrary fluid is an open problem in mathematics and of course, a very good modelling of such this fluid is strongly related to the membrane where the fluid flows on it. The blood as a complicated and Non-Newtonian fluid through the heart's chambers and heart's valves is one of the big challenges among mathematical-, medical-, physical- and computer-sciences. So far a lot of studies of the blood flowing through the heart have been attempted by various simple assumptions.

For instance, U.S. Pat. No. 5,537,641, assigned to University of Central Florida Research Foundation, Inc. discloses a method for generating a three-dimensional animation model that stimulates a fluid flow on a three-dimensional graphics display. The said patent does not extend the solution of Navier-Stokes equation to non-Newtonian fluids like blood explicitly.

U.S. Pat. No. 6,135,957 assigned to U.S. Philips Corporation describes a method of determining the viscosity and the pressure gradient in a blood vessel, including the acquisition of n≧2 blood speed values, corresponding to the same number of n radii of the blood vessel, determined along a diameter situated in a given axial position, formation of a blood speed vector by means of said n blood speed values, and evaluation of said viscosity and pressure gradient on the basis of a transformation of said blood speed value, including formation of a linear relation which directly links a flow rate vector (y) to the speed derivative vector (h), factorized by the viscosity (μ), and to the pressure gradient vector (σ), and simultaneous evaluation of the two values to be determined for the viscosity (μ) and the pressure gradient (σ) on the basis of said direct equation. The said method, as disclosed in U.S. '957, specifically used to determine blood speed, but seemingly does not disclose a method or system for modelling cardiac condition, specifically left ventricle having a main role in cardiac function based on flow.

Hence, the present inventors propose a novel system for solution of Navier-Stokes to model not only the normal blood flow inside the left ventricle but also for the other cavities and valves and model heart diseases.

SUMMARY OF INVENTION

The invention provides method for studying the blood flows regionally near echocardiography samples and globally inside the left ventricle.

In an aspect, according to current invention, the blood flow curves are regionally investigated near the neighbourhoods of echocardiography samples that is, the basal, mid and apical anterior, the basal, mid and apical inferior, and the basal, mid and apical lateral, the basal, mid and apical septum.

In another aspect, the flow curves investigated hereinabove are used to model heart diseases using echocardiography.

BRIEF DESCRIPTION OF DRAWINGS

FIG. 1 shows a general flowchart of this invention.

FIG. 2 shows a flowchart where states the basal, mid and apical Anterior as three echocardiography samples in the left ventricle, in their corresponded regions.

FIG. 3 shows three rendering of the basal, mid and apical anterior in their corresponded regions.

FIG. 4 shows a flowchart that models the blood flow curve near a neighbourhood of the basal Anterior in the myocardium of the left ventricle.

FIG. 5 shows the blood flow curve near the corresponded neighbourhood of the basal anterior in the myocardium of the left ventricle where has been rendered at Mathlab software.

FIG. 6 shows a flowchart that models the blood flow curve near a neighbourhood of the mid Anterior in the myocardium of the left ventricle.

FIG. 7 shows the blood flow curve near the corresponded neighborhood of the mid anterior in the myocardium of the left ventricle where has been rendered at Mathlab software.

FIG. 8 shows a flowchart that models the blood flow curve near a neighborhood of the apical Anterior in the myocardium of the left ventricle.

FIG. 9 shows the blood flow curve near the corresponded neighborhood of the mid anterior in the myocardium of the left ventricle where has been rendered at Mathlab software.

FIG. 10 shows a flowchart where states the basal, mid and apical Inferior as three echocardiography samples in the left ventricle, in their corresponded regions.

FIG. 11 shows three rendering of the basal, mid and apical inferior in their corresponded regions at Mathlab software.

FIG. 12 shows a flowchart that models the blood flow curve near a neighbourhood of the apical Inferior in the myocardium of the left ventricle.

FIG. 13 shows the blood flow curve near the corresponded neighbourhood of the apical Inferior in the myocardium of the left ventricle where has been rendered at Mathlab software.

FIG. 14 shows a flowchart that models the blood flow curve near a neighborhood of the mid Inferior in the myocardium of the left ventricle.

FIG. 15 shows the blood flow curve near the corresponded neighborhood of the mid Inferior in the myocardium of the left ventricle where has been rendered at Mathlab software.

FIG. 16 shows a flowchart that models the blood flow curve near a neighborhood of the basal Inferior in the myocardium of the left ventricle.

FIG. 17 shows the blood flow curve near the corresponded neighborhood of the basal Inferior in the myocardium of the left ventricle where has been rendered at Mathlab software.

FIG. 18 shows a flowchart where states the basal, mid and apical Lateral as three echocardiography samples in the left ventricle, in their corresponded regions.

FIG. 19 shows three rendering of the basal, mid and apical lateral in their corresponded regions at Mathlab software.

FIG. 20 shows a flowchart that models the blood flow curve near a neighborhood of the basal Lateral in the myocardium of the left ventricle.

FIG. 21 shows the blood flow curve near the corresponded neighborhood of the basal Lateral in the myocardium of the left ventricle where has been rendered at Mathlab software.

FIG. 22 shows a flowchart that models the blood flow curve near a neighborhood of the mid Lateral in the myocardium of the left ventricle.

FIG. 23 shows the blood flow curve near the corresponded neighborhood of the mid Lateral in the myocardium of the left ventricle where has been rendered at Mathlab software.

FIG. 24 shows a flowchart that models the blood flow curve near a neighborhood of the apical Lateral in the myocardium of the left ventricle.

FIG. 25 shows the blood flow curve near the corresponded neighborhood of the apical Lateral in the myocardium of the left ventricle where has been rendered at Mathlab software.

FIG. 26 shows a flowchart where states the basal, mid and apical Septum as three echocardiography samples in the left ventricle, in their corresponded regions.

FIG. 27 shows three rendering of the basal, mid and apical septum in their corresponded regions at Mathlab software.

FIG. 28 shows a flowchart that models the blood flow curve near a neighborhood of the apical Septum in the myocardium of the left ventricle.

FIG. 29 shows the blood flow curve near the corresponded neighborhood of the apical Septum in the myocardium of the left ventricle where has been rendered at Mathlab software.

FIG. 30 shows a flowchart that models the blood flow curve near a neighborhood of the mid Septum in the myocardium of the left ventricle.

FIG. 31 shows the blood flow curve near the corresponded neighborhood of the mid Septum in the myocardium of the left ventricle where has been rendered at Mathlab software.

FIG. 32 shows a flowchart that models the blood flow curve near a neighborhood of the basal Septum in the myocardium of the left ventricle.

FIG. 33 shows the blood flow curve near the corresponded neighborhood of the basal Septum in the myocardium of the left ventricle where has been rendered at Mathlab software.

FIG. 34 shows a flowchart where states the blood flow curve inside the left ventricle is regionally made by gluing together blood flow curves that have been modeled near echocardiography samples.

FIG. 35 shows the 2-D blood flow curve view in the Mathlab software.

FIG. 36 shows the flow of the blood inside the left ventricle related to the other works.

FIG. 37 shows two blood flow curves from the left to the right one near a small shant in the Mathlab software.

FIG. 38 shows blood flow curves from the left to the right near two shants at VSD in Mathlab software.

FIG. 39 the first shows the blood flow curve after an anti-anatomic prosthetic Mitral valve replacement and the second shows the blood flow curves for the natural Mitral valve at the left and after an anatomic prosthetic Mitral valve replacement at the right respectively.

FIG. 40 shows the blood flow curve after the best prosthetic Mitral valve replacement.

DETAILED DESCRIPTION OF INVENTION

The invention will now be described in details with reference to various preferred and optional embodiments to make the invention clear.

The present invention describes a method for solving the Navier-Stocks equations of the blood dynamic as a Non-Newtonian fluid in the left ventricle for modeling of the myocardial motion in an elastic membrane.

In an embodiment the invention provides modelling of the blood flow curves inside the left ventricle by studying the flow of the blood curves near echocardiography samples i.e. the basal, mid and apical Anterior and the basal, mid and apical Inferior and the basal, mid and apical Lateral and the basal, mid and apical Septum. These samples as the material elastic points in the myocardium of the left ventricle induce mechanical parameters to the viscosity of blood.

Invention describes method of formulating and calculating the mechanical parameters of blood, numerically, and then applying Navier-Stocks equations to model the blood flow curve regionally and globally inside the left ventricle. The method is summarized as below

a. Calculating mechanical parameters of blood near echocardiography samples;

b. calculating the myofiber curve for echocardiography samples of step (a);

c. studying “quadratic form” for the curve of step (b) for each echocardiography samples;

d. determining the blood flow curve for step (c) for each echocardiography samples and

e. integrating the blood flow curves of step (d) for determining blood flow curve for left ventricle globally.

In an embodiment of invention, FIG. 2 illustrates a flowchart giving mathematical signs of the basal Anterior and the mid of Anterior and the apical Anterior in their corresponded regions to obtain good formulizations of the induced mechanical parameters of the blood.

Referring to FIG. 3, invention further describes geometrical modeling of the basal, mid and apical Anterior using Mathlab software as described below.

let ε_(rr, P) _(bA) , ε_(ll, P) _(bA) and ε_(cc, P) _(bA) be strain components of the basal Anterior, P_(bA) we set

γ_(P) _(bA) ={each mayocardial sample X that ε_(rr, X)×ε_(ll, X)=ε_(rr, P) _(bA) ×ε_(ll, P) _(bA) and ε_(rr, X)×ε_(ll, X)×ε_(cc, X)=ε_(rr, P) _(bA) ×ε_(ll, P) _(bA) ×ε_(cc, P) _(bA) }

and similarly for the mid of Anterior and the apical Anterior would have the following sets;

γ_(P) _(mA) ={each mayocardial sample X that ε_(rr, X)×ε_(ll, X)=ε_(rr, P) _(mA) ×ε_(ll, P) _(mA) and ε_(rr, X)×ε_(ll, X)×ε_(cc, X)=ε_(rr, P) _(mA) ×ε_(ll, P) _(mA) ×ε_(cc, P) _(mA) }

γ_(P) _(aA) ={each mayocardial sample X that ε_(rr, X)×ε_(ll, X)=ε_(rr, P) _(aA) ×ε_(ll, P) _(aA) and ε_(rr, X)×ε_(ll, X)×ε_(cc, X)=ε_(rr, P) _(aA) ×ε_(ll, P) _(aA) ×ε_(cc, P) _(aA) }

In fact, γ_(P) _(bA′) γ_(P) _(mA) and γ_(P) _(aA) are those myofiber bands in the myocardium where have been called at FIG. 2.

In a preferred embodiment Q's at FIG. 3 have the following algebraic equations:

Q _(P) _(bA) :D _(P) _(bA) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y ₃ ²

D _(P) _(bA) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y _(1, bA) ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y _(2, bA) ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y _(3, bA) ²

Where, P_(k) and P_(l) are points belonging to γ_(P) _(bA) ∩ O_(P) _(bA) and if P_(bA)=(y_(1, bA), y_(2, bA), y_(3, bA)) as Cartesian coordinate.

By a similar argument we have the algebraic equations in Cartesian coordinate of Q's for the mid of Anterior and the apical Anterior:

For the mid of Anterior:

Q _(P) _(mA) :D _(P) _(mA) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y ₃ ²

D _(P) _(mA) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y _(1, mA) ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y _(2, mA) ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y _(3, mA) ²

Where, P_(k) and P_(l) are points belonging to γ_(P) _(mA) ∩ O_(P) _(mA) and if P_(mA)=(y_(1, mA), y_(2, mA), y_(3, mA)) as Cartesian coordinate.

For apical Anterior:

Q _(P) _(aA) :D _(P) _(aA) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y ₃ ²

D _(P) _(aA) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y _(1, aA) ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y _(2, aA) ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y _(3, aA) ²

Where, P_(k) and P_(l) are points belonging to γ_(P) _(aA) ∩ O_(P) _(aA) and if P_(aA)=(y_(1, aA), y_(2, aA), y_(3, aA)) as Cartesian coordinate.

In a preferred embodiment, the invention provides an analytical solution of the Navier-Stocks equations in the region O_(P) _(mA) of the apical Inferior. FIG. 5 shows a rendering of these solutions in the mathlab software.

FIG. 4 shows the mechanical parameters of blood which were induced by Q_(P) _(mA) in region O_(P) _(mA) related to apical inferior. The surface is;

F _(P) _(bA) ((y ₁ , y ₂ , y ₃))=(Σ_(k, l)ε_(rr P) _(k) ′_(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) ′_(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) ′_(, P) _(l) dt)·y ₃ ² −D _(P) _(bA)

In the region O_(P) _(bA) , let φ_(1, P) _(bA) (t), φ_(2, P) _(bA) (t) and φ_(3, P) _(bA) (t) are parameterized forms of the projections of the surface F_(P) _(bA) on xy-axis and yz-axis:

${{\phi_{1,P_{bA}}(t)} = \left( {t,\left( {\left( {D_{P_{bA}} - {\left( {\sum\limits_{k,l}{ɛ_{{rr}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${{\phi_{2,P_{bA}}(t)} = \left( {t,\left( {\left( {D_{P_{bA}} - {\left( {\sum\limits_{k,l}{ɛ_{{rr}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{cc}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${\phi_{3,P_{bA}}(t)} = \left( {t,\left( {\left( {D_{P_{bA}} - {\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{cc}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)$

Following formulae were set;

T _(1, P) _(bA) (t)=φ_(1, P) _(bA) (t)′/|φ_(1, P) _(bA) (t)′|;

S _(1, P) _(bA) =∫_(t) _(o) ^(t)φ_(1, P) _(bA) (u)′ du;

$\begin{matrix} {\mspace{79mu} {{{{\kappa_{1,P_{bA}}(t)} \cdot {N_{1,P_{bA}}(t)}} = \frac{T_{1,P_{bA}}}{s}};}} \\ {{{\kappa_{1,P_{bA}}(t)} = {\left( \left( {\left( {D_{P_{bA}} - {\left( {\sum\limits_{k,l}{ɛ_{{rr}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,P_{bA}^{\prime 3}}}}};} \end{matrix}$ a _(1, P) _(bA) (t)=S _(1, P) _(bA) ″·T _(1, P) _(bA) (t)+κ_(1, P) _(bA) (t)·N _(1, P) _(bA) (t)

T _(2, P) _(bA) (t)=φ_(2, P) _(bA) (t)′/|φ_(2, P) _(bA) (t)′|;

S _(2, P) _(bA) =∫_(t) _(o) ^(t)φ_(2, P) _(bA) (u)′ du;

$\begin{matrix} {\mspace{79mu} {{{{\kappa_{2,P_{bA}}(t)} \cdot {N_{2,P_{bA}}(t)}} = \frac{T_{2,P_{bA}}}{s}};}} \\ {{{\kappa_{2,P_{bA}}(t)} = {\left( \left( {\left( {D_{P_{bA}} - {\left( {\sum\limits_{k,l}{ɛ_{{rr}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{cc}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,P_{bA}^{\prime 3}}}}};} \end{matrix}$ a _(2, P) _(bA) (t)=S _(2, P) _(bA) ″·T _(2, P) _(bA) (t)+κ_(2, P) _(bA) (t)·N _(2, P) _(bA) (t)

T _(3, P) _(bA) (t)=φ_(3, P) _(bA) (t)′/|φ_(3, P) _(bA) (t)′|;

S _(3, P) _(bA) =∫_(t) _(o) ^(t)φ_(3, P) _(bA) (u)′ du;

$\begin{matrix} {\mspace{79mu} {{{{\kappa_{3,P_{bA}}(t)} \cdot {N_{3,P_{bA}}(t)}} = \frac{T_{2,P_{bA}}}{s}};}} \\ {{{\kappa_{3,P_{bA}}(t)} = {\left( \left( {\left( {D_{P_{bA}} - {\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,P_{bA}^{\prime 3}}}}};} \end{matrix}$ a _(3, P) _(bA) (t)=S _(3, P) _(bA) ·T _(3, P) _(bA) (t)+κ_(3, P) _(bA) (t)·N _(3, P) _(bA) (t)

If (x₁, x₂, x₃, t) is the coordinate system of the red blood cell in a neighbourhood O_(P) _(bA) of the basal anterior and δ(x₁, x₂, x₃, t)=δ*(x₁, t)·δ*(x₂, t)·δ*(x₃, t) where δ* is the dirac function and C_(1, P) _(bA) , C_(2, P) _(bA) and C_(3, P) _(bA) are the graphs of φ_(1, P) _(bA) (t), φ_(2, P) _(bA) (t) and φ_(3, P) _(bA) (t) respectively then the mechanical parameters of the red blood cells in the region O_(P) _(bA) are realized by the following formulas:

v _(1, P) _(bA) (t)=∫_(C) ₁ _(, P) _(bA) T _(1, P) _(bA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(1, P) _(bA) (t)=∫_(C) ₁ _(, P) _(bA) N _(1, P) _(bA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(1, P) _(bA) ^(RBC)(t)=∫_(C) ₁ _(, P) _(bA) a _(1, P) _(bA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(2, P) _(bA) (t)=∫_(C) ₂ _(, P) _(bA) T _(2, P) _(bA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(2, P) _(bA) (t)=∫_(C) ₂ _(, P) _(bA) N _(2, P) _(bA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(2, P) _(bA) ^(RBC)(t)=∫_(C) ₂ _(, P) _(bA) a _(2, P) _(bA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(3, P) _(bA) (t)=∫_(C) ₃ _(, P) _(bA) T _(3, P) _(bA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(3, P) _(bA) (t)=∫_(C) ₃ _(, P) _(bA) N _(3, P) _(bA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(3, P) _(bA) ^(RBC)(t)=∫_(C) ₃ _(, P) _(bA) a _(3, P) _(bA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

the formulas as mentioned hereinabove give analytical solution of the Navier-Stocks equations in the region O_(P) _(bA) of the basal Anterior. The invention provides, with reference to FIG. 5, provides a rendering of this solution in the mathlab software.

In a preferred embodiment, the invention provides an analytical solution of the Navier-Stocks equations in the region O_(P) _(mA) of the apical Inferior. FIG. 7 shows a rendering of these solutions in the mathlab software.

FIG. 6 shows the mechanical parameters of blood which were induced by Q_(P) _(mA) in region O_(P) _(mA) related to apical inferior. The surface is;

F _(P) _(mA) ((y ₁ , y ₂ , y ₃))=(Σ_(k, l)ε_(rr P) _(k) ′_(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) ′_(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) ′_(, P) _(l) dt)·y ₃ ² −D _(P) _(mA)

In the region O_(P) _(mA) , let φ_(1, P) _(mA) (t), φ_(2, P) _(mA) (t) and φ_(3, P) _(mA) (t) are parameterized forms of the projections of the surface F_(P) _(mA) on xy-axis and yz-axis:

${{\phi_{1,P_{mA}}(t)} = \left( {t,\left( {\left( {D_{P_{mA}} - {\left( {\sum\limits_{k,l}{ɛ_{{rr}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${{\phi_{2,P_{mA}}(t)} = \left( {t,\left( {\left( {D_{P_{mA}} - {\left( {\sum\limits_{k,l}{ɛ_{{rr}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{cc}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${\phi_{3,P_{mA}}(t)} = \left( {t,\left( {\left( {D_{P_{mA}} - {\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{cc}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)$

Following formulae were set;

T _(1, P) _(mA) (t)=φ_(1, P) _(mA) (t)′/|φ_(1, P) _(mA) (t)′|;

S _(1, P) _(mA) =∫_(t) _(o) ^(t)φ_(1, P) _(mA) (u)′ du;

$\begin{matrix} {\mspace{79mu} {{{{\kappa_{1,P_{mA}}(t)} \cdot {N_{1,P_{mA}}(t)}} = \frac{T_{1,P_{mA}}}{s}};}} \\ {{{\kappa_{1,P_{mA}}(t)} = {\left( \left( {\left( {D_{P_{mA}} - {\left( {\sum\limits_{k,l}{ɛ_{{rr}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,P_{mA}^{\prime 3}}}}};} \end{matrix}$ a _(1, P) _(mA) (t)=S _(1, P) _(mA) ″·T _(1, P) _(mA) (t)+κ_(1, P) _(mA) (t)·N _(1, P) _(mA) (t)

T _(2, P) _(mA) (t)=φ_(2, P) _(mA) (t)′/|φ_(2, P) _(mA) (t)′|;

S _(2, P) _(mA) =∫_(t) _(o) ^(t)φ_(2, P) _(mA) (u)′ du;

$\begin{matrix} {\mspace{79mu} {{{{\kappa_{2,P_{mA}}(t)} \cdot {N_{2,P_{mA}}(t)}} = \frac{T_{2,P_{mA}}}{s}};}} \\ {{{\kappa_{2,P_{mA}}(t)} = {\left( \left( {\left( {D_{P_{mA}} - {\left( {\sum\limits_{k,l}{ɛ_{{rr}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{cc}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,P_{mA}^{\prime 3}}}}};} \end{matrix}$ a _(2, P) _(mA) (t)=S _(2, P) _(mA) ″·T _(2, P) _(mA) (t)+κ_(2, P) _(mA) (t)·N _(2, P) _(mA) (t)

T _(3, P) _(mA) (t)=φ_(3, P) _(mA) (t)′/|φ_(3, P) _(mA) (t)′|;

S _(3, P) _(mA) =∫_(t) _(o) ^(t)φ_(3, P) _(mA) (u)′ du;

$\begin{matrix} {\mspace{79mu} {{{{\kappa_{3,P_{mA}}(t)} \cdot {N_{3,P_{mA}}(t)}} = \frac{T_{2,P_{mA}}}{s}};}} \\ {{{\kappa_{3,P_{mA}}(t)} = {\left( \left( {\left( {D_{P_{mA}} - {\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,P_{mA}^{\prime 3}}}}};} \end{matrix}$ a _(3, P) _(mA) (t)=S _(3, P) _(mA) ·T _(3, P) _(mA) (t)+κ_(3, P) _(mA) (t)·N _(3, P) _(mA) (t)

If (x₁, x₂, x₃, t) is the coordinate system of the red blood cell in a neighbourhood O_(P) _(mA) of the basal anterior and δ(x₁, x₂, x₃, t)=δ*(x₁, t)·δ*(x₂, t)·δ*(x₃, t) where δ* is the dirac function and C_(1, P) _(mA) , C_(2, P) _(mA) and C_(3, P) _(mA) are the graphs of φ_(1, P) _(mA) (t), φ_(2, P) _(mA) (t) and φ_(3, P) _(mA) (t) respectively then the mechanical parameters of the red blood cells in the region O_(P) _(mA) are realized by the following formulas:

v _(1, P) _(mA) (t)=∫_(C) ₁ _(, P) _(mA) T _(1, P) _(mA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(1, P) _(mA) (t)=∫_(C) ₁ _(, P) _(mA) N _(1, P) _(mA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(1, P) _(mA) ^(RBC)(t)=∫_(C) ₁ _(, P) _(mA) a _(1, P) _(mA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(2, P) _(mA) (t)=∫_(C) ₂ _(, P) _(mA) T _(2, P) _(mA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(2, P) _(mA) (t)=∫_(C) ₂ _(, P) _(mA) N _(2, P) _(mA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(2, P) _(mA) ^(RBC)(t)=∫_(C) ₂ _(, P) _(mA) a _(2, P) _(mA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(3, P) _(mA) (t)=∫_(C) ₃ _(, P) _(mA) T _(3, P) _(mA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(3, P) _(mA) (t)=∫_(C) ₃ _(, P) _(mA) N _(3, P) _(mA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(3, P) _(mA) ^(RBC)(t)=∫_(C) ₃ _(, P) _(mA) a _(3, P) _(mA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

In a preferred embodiment, the invention provides an analytical solution of the Navier-Stocks equations in the region O_(P) _(aA) of the apical Inferior. FIG. 9 shows a rendering of these solutions in the mathlab software.

FIG. 8 shows the mechanical parameters of blood which were induced by Q_(P) _(aA) in region O_(P) _(aA) related to apical inferior. The surface is;

F _(P) _(aA) ((y ₁ , y ₂ , y ₃))=(Σ_(k, l)ε_(rr P) _(k) ′_(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) ′_(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) ′_(, P) _(l) dt)·y ₃ ² −D _(P) _(mA)

In the region O_(P) _(aA) , let φ_(1, P) _(aA) (t), φ_(2, P) _(aA) (t) and φ_(3, P) _(aA) (t) are parameterized forms of the projections of the surface F_(P) _(aA) on xy-axis and yz-axis:

${{\phi_{1,P_{aA}}(t)} = \left( {t,\left( {\left( {D_{P_{aA}} - {\left( {\sum\limits_{k,l}{ɛ_{{rr}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${{\phi_{2,P_{aA}}(t)} = \left( {t,\left( {\left( {D_{P_{aA}} - {\left( {\sum\limits_{k,l}{ɛ_{{rr}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{cc}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${\phi_{3,P_{aA}}(t)} = \left( {t,\left( {\left( {D_{P_{aA}} - {\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{cc}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)$

Following formulae were set;

T _(1, P) _(aA) (t)=φ_(1, P) _(aA) (t)′/|φ_(1, P) _(aA) (t)′|;

S _(1, P) _(aA) =∫_(t) _(o) ^(t)φ_(1, P) _(aA) (u)′ du;

$\begin{matrix} {\mspace{79mu} {{{{\kappa_{1,P_{aA}}(t)} \cdot {N_{1,P_{aA}}(t)}} = \frac{T_{1,P_{aA}}}{s}};}} \\ {{{\kappa_{1,P_{aA}}(t)} = {\left( \left( {\left( {D_{P_{aA}} - {\left( {\sum\limits_{k,l}{ɛ_{{rr}_{P_{k},P_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,P_{aA}^{\prime 3}}}}};} \end{matrix}$ a _(1, P) _(aA) (t)=S _(1, P) _(aA) ″·T _(1, P) _(aA) (t)+κ_(1, P) _(aA) (t)·N _(1, P) _(aA) (t)

T _(2, P) _(aA) (t)=φ_(2, P) _(aA) (t)′/|φ_(2, P) _(aA) (t)′|;

S _(2, P) _(aA) =∫_(t) _(o) ^(t)φ_(2, P) _(aA) (u)′ du;

$\mspace{79mu} {{{{\kappa_{2,p_{aA}}(t)} \cdot {N_{2,p_{aA}}(t)}} = \frac{T_{2,p_{aA}}}{s}};}$ ${{\kappa_{2,p_{aA}}(t)} = {\left( \left( {\left( {D_{p_{aA}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,p_{aA}}^{\,^{\prime}3}}}};$ a _(2, P) _(aA) (t)=S _(2, P) _(aA) ″·T _(2, P) _(aA) (t)+κ_(2, P) _(aA) (t)·N _(2, P) _(aA) (t)

T _(3, P) _(aA) (t)=φ_(3, P) _(aA) (t)′/|φ_(3, P) _(aA) (t)′|;

S _(3, P) _(aA) =∫_(t) _(o) ^(t)φ_(3, P) _(aA) (u)′ du;

$\mspace{79mu} {{{{\kappa_{3,p_{aA}}(t)} \cdot {N_{3,p_{aA}}(t)}} = \frac{T_{2,p_{aA}}}{s}};}$ ${{\kappa_{3,p_{aA}}(t)} = {\left( \left( {\left( {D_{p_{aA}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,p_{aA}}^{\,^{\prime}3}}}};$ a _(3, P) _(aA) (t)=S _(3, P) _(aA) ·T _(3, P) _(aA) (t)+κ_(3, P) _(aA) (t)·N _(3, P) _(aA) (t)

If (x₁, x₂, x₃, t) is the coordinate system of the red blood cell in a neighbourhood O_(P) _(mA) of the basal anterior and δ(x₁, x₂, x₃, t)=δ*(x₁, t)·δ*(x₂, t)·δ*(x₃, t) where δ* is the dirac function and C_(1, P) _(aA) , C_(2, P) _(aA) and C_(3, P) _(aA) are the graphs of φ_(1, P) _(aA) (t), φ_(2, P) _(aA) (t) and φ_(3, P) _(aA) (t) respectively then the mechanical parameters of the red blood cells in the region O_(P) _(mA) are realized by the following formulas:

v _(1, P) _(aA) (t)=∫_(C) ₁ _(, P) _(aA) T _(1, P) _(aA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(1, P) _(aA) (t)=∫_(C) ₁ _(, P) _(aA) N _(1, P) _(aA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(1, P) _(aA) ^(RBC)(t)=∫_(C) ₁ _(, P) _(aA) a _(1, P) _(aA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(2, P) _(aA) (t)=∫_(C) ₂ _(, P) _(aA) T _(2, P) _(aA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(2, P) _(aA) (t)=∫_(C) ₂ _(, P) _(aA) N _(2, P) _(aA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(2, P) _(aA) ^(RBC)(t)=∫_(C) ₂ _(, P) _(aA) a _(2, P) _(aA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(3, P) _(aA) (t)=∫_(C) ₃ _(, P) _(aA) T _(3, P) _(aA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(3, P) _(aA) (t)=∫_(C) ₃ _(, P) _(aA) N _(3, P) _(aA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(3, P) _(aA) ^(RBC)(t)=∫_(C) ₃ _(, P) _(aA) a _(3, P) _(aA) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

In an embodiment the invention provides mathematical signs of the basal Inferior and the mid of Inferior and the apical Inferior in their corresponded regions to gain good formulizations of the induced mechanical parameters of the blood, as shown in FIG. 10.

Accordingly, let ε_(rr, P) _(bl) , ε_(ll, P) _(bl) and ε_(cc, P) _(bl) be the strain components of the basal Inferior P_(bl), then

γ_(P) _(bl) ={each mayocardial sample X that ε_(rr, X)×ε_(ll, X)=ε_(rr, P) _(bl) ×ε_(ll, P) _(bl) and ε_(rr, X)×ε_(ll, X)×ε_(cc, X)=ε_(rr, P) _(bl) ×ε_(ll, P) _(bl) ×ε_(cc, P) _(bl) }

similarly for mid and apical inferior the sets are:

γ_(P) _(ml) ={each mayocardial sample X that ε_(rr, X)×ε_(ll, X)=ε_(rr, P) _(ml) ×ε_(ll, P) _(ml) and ε_(rr, X)×ε_(ll, X)×ε_(cc, X)=ε_(rr, P) _(ml) ×ε_(ll, P) _(ml) ×ε_(cc, P) _(ml) }

γ_(P) _(al) ={each mayocardial sample X that ε_(rr, X)×ε_(ll, X)=ε_(rr, P) _(al) ×ε_(ll, P) _(al) and ε_(rr, X)×ε_(ll, X)×ε_(cc, X)=ε_(rr, P) _(al) ×ε_(ll, P) _(al) ×ε_(cc, P) _(al) }

γ_(P) _(bl) , γ_(P) _(ml) and γ_(P) _(al) are the myofiber bands illustrated in FIG. 2. The Q's have following values

Q _(P) _(bl) :D _(P) _(bl) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y ₃ ²

D _(P) _(bl) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y _(1, bl) ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y _(2, bl) ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y _(3, bl) ²

Where, P_(k) and P_(l) are points belonging to γ_(P) _(bl) ∩ O_(P) _(bl) and if P_(bl)=(y_(1, bl), y_(2, bl), y_(3, bl)) as Cartesian coordinate

Similarly, the Cartesian coordinates for Q's for mid and apical Inferiors are as follows;

For the mid of Anterior:

Q _(P) _(ml) :D _(P) _(ml) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y ₃ ²

D _(P) _(ml) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y _(1, ml) ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y _(2, ml) ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y _(3, ml) ²

where, P_(k) and P_(l) are points belonging to γ_(P) _(ml) ∩ O_(P) _(ml) and if P_(ml)=(y_(1, ml), y_(2, ml), y_(3, ml)) as Cartesian coordinate.

For apical Anterior:

Q _(P) _(al) :D _(P) _(al) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y ₃ ²

D _(P) _(al) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y _(1, al) ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y _(2, al) ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y _(3, al) ²

where, P_(k) and P_(l) are points belonging to γ_(P) _(al) ∩ O_(P) _(al) and if P_(al)=(y_(1, al), y_(2, al), y_(3, al)) as Cartesian coordinate.

In a preferred embodiment, the invention provides an analytical solution of the Navier-Stocks equations in the region O_(P) _(al) of the apical Inferior. FIG. 13 shows a rendering of these solutions in the mathlab software.

FIG. 12 shows the mechanical parameters of blood which were induced by Q_(P) _(al) in region O_(P) _(al) related to apical inferior. The surface is;

F _(P) _(al) ((y ₁ , y ₂ , y ₃))=(Σ_(k, l)ε_(rr P) _(k) ′_(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) ′_(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) ′_(, P) _(l) dt)·y ₃ ² −D _(P) _(al)

In the region O_(P) _(al) , let φ_(1, P) _(al) (t), φ_(2, P) _(al) (t) and φ_(3, P) _(al) (t) are parameterized forms of the projections of the surface F_(P) _(al) on xy-axis and yz-axis:

${{\phi_{1,p_{al}}(t)} = \left( {t,\left( {\left( {D_{p_{al}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${{\phi_{2,p_{al}}(t)} = \left( {t,\left( {\left( {D_{p_{al}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${\phi_{3,p_{al}}(t)} = \left( {t,\left( {\left( {D_{p_{al}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}}} \right)$

Following formulae were set;

T _(1, P) _(al) (t)=φ_(1, P) _(al) (t)′/|φ_(1, P) _(al) (t)′|;

S _(1, P) _(al) =∫_(t) _(o) ^(t)φ_(1, P) _(al) (u)′ du;

$\mspace{79mu} {{{{\kappa_{1,p_{al}}(t)} \cdot {N_{1,p_{al}}(t)}} = \frac{T_{1,p_{al}}}{s}};}$ ${{\kappa_{1,p_{al}}(t)} = {\left( \left( {\left( {D_{p_{al}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,p_{al}}^{\,^{\prime}3}}}};$ a _(1, P) _(al) (t)=S _(1, P) _(al) ″·T _(1, P) _(al) (t)+κ_(1, P) _(al) (t)·N _(1, P) _(al) (t)

T _(2, P) _(al) (t)=φ_(2, P) _(al) (t)′/|φ_(2, P) _(al) (t)′|;

S _(2, P) _(al) =∫_(t) _(o) ^(t)φ_(2, P) _(al) (u)′ du;

$\mspace{79mu} {{{{\kappa_{2,p_{al}}(t)} \cdot {N_{2,p_{al}}(t)}} = \frac{T_{2,p_{al}}}{s}};}$ ${{\kappa_{2,p_{al}}(t)} = {\left( \left( {\left( {D_{p_{al}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,p_{al}}^{\,^{\prime}3}}}};$ a _(2, P) _(al) (t)=S _(2, P) _(al) ″·T _(2, P) _(al) (t)+κ_(2, P) _(al) (t)·N _(2, P) _(al) (t)

T _(3, P) _(al) (t)=φ_(3, P) _(al) (t)′/|φ_(3, P) _(al) (t)′|;

S _(3, P) _(al) =∫_(t) _(o) ^(t)φ_(3, P) _(al) (u)′ du;

$\mspace{79mu} {{{{\kappa_{3,p_{al}}(t)} \cdot {N_{3,p_{al}}(t)}} = \frac{T_{2,p_{al}}}{s}};}$ ${{\kappa_{3,p_{al}}(t)} = {\left( \left( {\left( {D_{p_{al}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,p_{al}}^{\,^{\prime}3}}}};$ a _(3, P) _(al) (t)=S _(3, P) _(al) ·T _(3, P) _(al) (t)+κ_(3, P) _(al) (t)·N _(3, P) _(al) (t)

(x₁, x₂, x₃, t) is the coordinate system of the red blood cell in a neighbourhood O_(P) _(al) of the apical Inferior and δ(x₁, x₂, x₃, t)=δ*(x₁, t)·δ*(x₂, t)·δ*(x₃, t) where δ* is the dirac function and C_(1, P) _(al) , C_(2, P) _(al) and C_(3, P) _(al) are the graphs of φ_(1, P) _(al) (t), φ_(2, P) _(al) (t) and φ_(3, P) _(al) (t) respectively then the mechanical parameters of the red blood cells in the region O_(P) _(al) are calculated by the following formulae:

v _(1, P) _(al) (t)=∫_(C) ₁ _(, P) _(al) T _(1, P) _(al) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(1, P) _(al) (t)=∫_(C) ₁ _(, P) _(al) N _(1, P) _(al) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(1, P) _(al) ^(RBC)(t)=∫_(C) ₁ _(, P) _(al) a _(1, P) _(al) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(2, P) _(al) (t)=∫_(C) ₂ _(, P) _(al) T _(2, P) _(al) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(2, P) _(al) (t)=∫_(C) ₂ _(, P) _(al) N _(2, P) _(al) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(2, P) _(al) ^(RBC)(t)=∫_(C) ₂ _(, P) _(al) a _(2, P) _(al) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(3, P) _(al) (t)=∫_(C) ₃ _(, P) _(al) T _(3, P) _(al) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(3, P) _(al) (t)=∫_(C) ₃ _(, P) _(al) N _(3, P) _(al) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(3, P) _(al) ^(RBC)(t)=∫_(C) ₃ _(, P) _(al) a _(3, P) _(al) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

In another preferred embodiment the invention provides an analytical solution of the Navier-Stocks equations in the region O_(P) _(ml) of the mid Inferior. FIG. 15 shows a rendering of these solutions in the mathlab software.

FIG. 14 shows the mechanical parameters of blood which were induced by Q_(P) _(ml) in region O_(P) _(ml) related to apical inferior. The surface is;

F _(P) _(ml) ((y ₁ , y ₂ , y ₃))=(Σ_(k, l)ε_(rr P) _(k) ′_(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) ′_(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) ′_(, P) _(l) dt)·y ₃ ² −D _(P) _(ml)

In the region O_(P) _(ml) , let φ_(1, P) _(ml) (t), φ_(2, P) _(ml) (t) and φ_(3, P) _(ml) (t) are parameterized forms of the projections of the surface F_(P) _(ml) on xy-axis and yz-axis:

${{\phi_{1,p_{ml}}(t)} = \left( {t,\left( {\left( {D_{p_{ml}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${{\phi_{2,p_{ml}}(t)} = \left( {t,\left( {\left( {D_{p_{ml}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${\phi_{3,p_{ml}}(t)} = \left( {t,\left( {\left( {D_{p_{ml}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}}} \right)$

Following formulae were set;

T _(1, P) _(ml) (t)=φ_(1, P) _(ml) (t)′/|φ_(1, P) _(ml) (t)′|;

S _(1, P) _(ml) =∫_(t) _(o) ^(t)φ_(1, P) _(ml) (u)′ du;

$\mspace{79mu} {{{{\kappa_{1,p_{ml}}(t)} \cdot {N_{1,p_{ml}}(t)}} = \frac{T_{1,p_{ml}}}{s}};}$ ${{\kappa_{1,p_{ml}}(t)} = {\left( \left( {\left( {D_{p_{ml}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,p_{ml}}^{\,^{\prime}3}}}};$ a _(1, P) _(ml) (t)=S _(1, P) _(ml) ″·T _(1, P) _(ml) (t)+κ_(1, P) _(ml) (t)·N _(1, P) _(ml) (t)

T _(2, P) _(ml) (t)=φ_(2, P) _(ml) (t)′/|φ_(2, P) _(ml) (t)′|;

S _(2, P) _(ml) =∫_(t) _(o) ^(t)φ_(2, P) _(ml) (u)′ du;

$\mspace{79mu} {{{{\kappa_{2,p_{ml}}(t)} \cdot {N_{2,p_{ml}}(t)}} = \frac{T_{2,p_{ml}}}{s}};}$ ${{\kappa_{2,p_{ml}}(t)} = {\left( \left( {\left( {D_{p_{ml}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,p_{ml}}^{\,^{\prime}3}}}};$ a _(2, P) _(ml) (t)=S _(2, P) _(ml) ″·T _(2, P) _(ml) (t)+κ_(2, P) _(ml) (t)·N _(2, P) _(ml) (t)

T _(3, P) _(ml) (t)=φ_(3, P) _(ml) (t)′/|φ_(3, P) _(ml) (t)′|;

S _(3, P) _(ml) =∫_(t) _(o) ^(t)φ_(3, P) _(ml) (u)′ du;

$\mspace{79mu} {{{{\kappa_{3,p_{ml}}(t)} \cdot {N_{3,p_{ml}}(t)}} = \frac{T_{2,p_{ml}}}{s}};}$ ${{\kappa_{3,p_{ml}}(t)} = {\left( \left( {\left( {D_{p_{ml}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,p_{ml}}^{\,^{\prime}3}}}};$ a _(3, P) _(ml) (t)=S _(3, P) _(ml) ·T _(3, P) _(ml) (t)+κ_(3, P) _(ml) (t)·N _(3, P) _(ml) (t)

(x₁, x₂, x₃, t) is the coordinate system of the red blood cell in a neighbourhood O_(P) _(ml) of the mid Inferior and δ(x₁, x₂, x₃, t)=δ*(x₁, t)·δ*(x₂, t)·δ*(x₃, t) where δ* is the dirac function and C_(1, P) _(ml) , C_(2, P) _(ml) and C_(3, P) _(ml) are the graphs of φ_(1, P) _(ml) (t), φ_(2, P) _(ml) (t) and φ_(3, P) _(ml) (t) respectively then the mechanical parameters of the red blood cells in the region O_(P) _(ml) are calculated by the following formulae:

v _(1, P) _(ml) (t)=∫_(C) ₁ _(, P) _(ml) T _(1, P) _(ml) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(1, P) _(ml) (t)=∫_(C) ₁ _(, P) _(ml) N _(1, P) _(ml) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(1, P) _(ml) ^(RBC)(t)=∫_(C) ₁ _(, P) _(ml) a _(1, P) _(ml) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(2, P) _(ml) (t)=∫_(C) ₂ _(, P) _(ml) T _(2, P) _(ml) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(2, P) _(ml) (t)=∫_(C) ₂ _(, P) _(ml) N _(2, P) _(ml) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(2, P) _(ml) ^(RBC)(t)=∫_(C) ₂ _(, P) _(ml) a _(2, P) _(ml) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(3, P) _(ml) (t)=∫_(C) ₃ _(, P) _(ml) T _(3, P) _(ml) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(3, P) _(ml) (t)=∫_(C) ₃ _(, P) _(ml) N _(3, P) _(ml) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(3, P) _(ml) ^(RBC)(t)=∫_(C) ₃ _(, P) _(ml) a _(3, P) _(ml) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

In a preferred embodiment, the invention provides an analytical solution of the Navier-Stocks equations in the region O_(P) _(bl) of the basal Inferior. FIG. 17 shows a rendering of these solutions in the mathlab software.

FIG. 16 shows the mechanical parameters of blood which were induced by Q_(P) _(bl) in region O_(P) _(bl) related to apical inferior. The surface is;

F _(P) _(bl) ((y ₁ , y ₂ , y ₃))=(Σ_(k, l)ε_(rr P) _(k) ′_(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) ′_(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) ′_(, P) _(l) dt)·y ₃ ² −D _(P) _(bl)

In the region O_(P) _(bl) , let φ_(1, P) _(bl) (t), φ_(2, P) _(bl) (t) and φ_(3, P) _(bl) (t) are parameterized forms of the projections of the surface F_(P) _(bl) on xy-axis and yz-axis:

${{\phi_{1,p_{bl}}(t)} = \left( {t,\left( {\left( {D_{p_{bl}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${{\phi_{2,p_{bl}}(t)} = \left( {t,\left( {\left( {D_{p_{bl}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${\phi_{3,p_{bl}}(t)} = \left( {t,\left( {\left( {D_{p_{bl}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}}} \right)$

Following formulae were set;

T _(1, P) _(bl) (t)=φ_(1, P) _(bl) (t)′/|φ_(1, P) _(bl) (t)′|;

S _(1, P) _(bl) =∫_(t) _(o) ^(t)φ_(1, P) _(bl) (u)′ du;

$\mspace{79mu} {{{{\kappa_{1,p_{bl}}(t)} \cdot {N_{1,p_{bl}}(t)}} = \frac{T_{1,p_{bl}}}{s}};}$ ${{\kappa_{1,p_{bl}}(t)} = {\left( \left( {\left( {D_{p_{bl}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,p_{bl}}^{\,^{\prime}3}}}};$ a _(1, P) _(bl) (t)=S _(1, P) _(bl) ″·T _(1, P) _(bl) (t)+κ_(1, P) _(bl) (t)·N _(1, P) _(bl) (t)

T _(2, P) _(bl) (t)=φ_(2, P) _(bl) (t)′/|φ_(2, P) _(bl) (t)′|;

S _(2, P) _(bl) =∫_(t) _(o) ^(t)φ_(2, P) _(bl) (u)′ du;

$\mspace{79mu} {{{{\kappa_{2,p_{bl}}(t)} \cdot {N_{2,p_{bl}}(t)}} = \frac{T_{2,p_{bl}}}{s}};}$ ${{\kappa_{2,p_{bl}}(t)} = {\left( \left( {\left( {D_{p_{bl}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,p_{bl}}^{\,^{\prime}3}}}};$ a _(2, P) _(bl) (t)=S _(2, P) _(bl) ″·T _(2, P) _(bl) (t)+κ_(2, P) _(bl) (t)·N _(2, P) _(bl) (t)

T _(3, P) _(bl) (t)=φ_(3, P) _(bl) (t)′/|φ_(3, P) _(bl) (t)′|;

S _(3, P) _(bl) =∫_(t) _(o) ^(t)φ_(3, P) _(bl) (u)′ du;

$\mspace{79mu} {{{{\kappa_{3,p_{bl}}(t)} \cdot {N_{3,p_{bl}}(t)}} = \frac{T_{2,p_{bl}}}{s}};}$ ${{\kappa_{3,p_{bl}}(t)} = {\left( \left( {\left( {D_{p_{bl}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,p_{bl}}^{\,^{\prime}3}}}};$ a _(3, P) _(bl) (t)=S _(3, P) _(bl) ·T _(3, P) _(bl) (t)+κ_(3, P) _(bl) (t)·N _(3, P) _(bl) (t)

(x₁, x₂, x₃, t) is the coordinate system of the red blood cell in a neighbourhood O_(P) _(bl) of the basal inferior and δ(x₁, x₂, x₃, t)=δ*(x₁, t)·δ*(x₂, t)·δ*(x₃, t) where δ* is the dirac function and C_(1, P) _(ml) , C_(2, P) _(ml) and C_(3, P) _(ml) are the graphs of φ_(1, P) _(bl) (t), φ_(2, P) _(bl) (t) and φ_(3, P) _(bl) (t) respectively then the mechanical parameters of the red blood cells in the region O_(P) _(bl) are calculated by the following formulae:

v _(1, P) _(bl) (t)=∫_(C) ₁ _(, P) _(bl) T _(1, P) _(bl) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(1, P) _(bl) (t)=∫_(C) ₁ _(, P) _(bl) N _(1, P) _(bl) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(1, P) _(bl) ^(RBC)(t)=∫_(C) ₁ _(, P) _(bl) a _(1, P) _(bl) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(2, P) _(bl) (t)=∫_(C) ₂ _(, P) _(bl) T _(2, P) _(bl) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(2, P) _(bl) (t)=∫_(C) ₂ _(, P) _(bl) N _(2, P) _(bl) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(2, P) _(bl) ^(RBC)(t)=∫_(C) ₂ _(, P) _(bl) a _(2, P) _(bl) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(3, P) _(bl) (t)=∫_(C) ₃ _(, P) _(bl) T _(3, P) _(bl) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(3, P) _(bl) (t)=∫_(C) ₃ _(, P) _(bl) N _(3, P) _(bl) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(3, P) _(bl) ^(RBC)(t)=∫_(C) ₃ _(, P) _(bl) a _(3, P) _(bl) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

In an embodiment, as illustrated in FIG. 18, the invention provides mathematical signs of basal Lateral, mid Lateral and apical Lateral to obtain good formulizations of the induced mathematical parameters of the blood.

The invention further provides geometrical modelling of the basal, mid and apical Lateral as described below;

Let ε_(rr, P) _(bL) , ε_(ll, P) _(bL) and ε_(cc, P) _(bL) be the strain components of the basal Inferior P_(bL), then

γ_(P) _(bL) ={each mayocardial sample X that ε_(rr, X)×ε_(ll, X)=ε_(rr, P) _(bL) ×ε_(ll, P) _(bL) and ε_(rr, X)×ε_(ll, X)×ε_(cc, X)=ε_(rr, P) _(bL) ×ε_(ll, P) _(bL) ×ε_(cc, P) _(bL) }

similarly for mid and apical inferior the sets are:

γ_(P) _(mL) ={each mayocardial sample X that ε_(rr, X)×ε_(ll, X)=ε_(rr, P) _(mL) ×ε_(ll, P) _(mL) and ε_(rr, X)×ε_(ll, X)×ε_(cc, X)=ε_(rr, P) _(mL) ×ε_(ll, P) _(mL) ×ε_(cc, P) _(mL) }

γ_(P) _(aL) ={each mayocardial sample X that ε_(rr, X)×ε_(ll, X)=ε_(rr, P) _(aL) ×ε_(ll, P) _(aL) and ε_(rr, X)×ε_(ll, X)×ε_(cc, X)=ε_(rr, P) _(aL) ×ε_(ll, P) _(aL) ×ε_(cc, P) _(aL) }

γ_(P) _(bL) , γ_(P) _(mL) and γ_(P) _(aL) are the myofiber bands illustrated in FIG. 2. The Q's have following values

Q _(P) _(bL) :D _(P) _(bL) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y ₃ ²

D _(P) _(bL) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y _(1, bL) ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y _(2, bL) ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y _(3, bL) ²

Where, P_(k) and P_(l) are points belonging to γ_(P) _(bL) ∩ O_(P) _(bL) and if P_(bL)=(y_(1, bL), y_(2, bL), y_(3, bL)) as Cartesian coordinate

Similarly, the Cartesian coordinates for Q's for mid and apical Inferiors are as follows;

For the mid of Anterior:

Q _(P) _(mL) :D _(P) _(mL) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y ₃ ²

D _(P) _(mL) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y _(1, mL) ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y _(2, mL) ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y _(3, mL) ²

where, P_(k) and P_(l) are points belonging to γ_(P) _(mL) ∩ O_(P) _(mL) and if P_(mL)=(y_(1, mL), y_(2, mL), y_(3, mL)) as Cartesian coordinate:

For apical Anterior:

Q _(P) _(aL) :D _(P) _(aL) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y ₃ ²

D _(P) _(aL) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y _(1, aL) ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y _(2, aL) ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y _(3, aL) ²

where, P_(k) and P_(l) are points belonging to γ_(P) _(aL) ∩ O_(P) _(aL) and if P_(aL)=(y_(1, aL), y_(2, aL), y_(3, aL)) as Cartesian coordinate.

In a preferred embodiment, the invention provides an analytical solution of the Navier-Stocks equations in the region O_(P) _(aL) of the apical Inferior. FIG. 21 shows a rendering of these solutions in the mathlab software.

FIG. 20, illustrates mechanical parameters of blood induced by Q_(P) _(aL) in the region O_(P) _(aL) related to apical Lateral. The surface parameters are as follows

F _(P) _(aL) ((y ₁ , y ₂ , y ₃))=(Σ_(k, l)ε_(rr P) _(k) ′_(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) ′_(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) ′_(, P) _(l) dt)·y ₃ ² −D _(P) _(aL)

In the region O_(P) _(aL) , let φ_(1, P) _(aL) (t), φ_(2, P) _(aL) (t) and φ_(3, P) _(aL) (t) are parameterized forms of the projections of the surface F_(P) _(aL) on xy-axis and yz-axis:

${{\phi_{1,p_{aL}}(t)} = \left( {t,\left( {\left( {D_{p_{aL}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${{\phi_{2,p_{aL}}(t)} = \left( {t,\left( {\left( {D_{p_{aL}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${\phi_{3,p_{aL}}(t)} = \left( {t,\left( {\left( {D_{p_{aL}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}}} \right)$

Following formulae were set;

T _(1, P) _(aL) (t)=φ_(1, P) _(aL) (t)′/|φ_(1, P) _(aL) (t)′|;

S _(1, P) _(aL) =∫_(t) _(o) ^(t)φ_(1, P) _(aL) (u)′ du;

$\mspace{79mu} {{{{k_{1,P_{aL}}(t)} \cdot {N_{1,P_{aL}}(t)}} = \frac{T_{1,P_{aL}}}{s}};}$ ${{k_{1,P_{aL}}(t)} = {\left( \left( {\left( {D_{P_{aL}} - {\left( {\sum\limits_{k,l}{ɛ_{{rrp}_{k},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,P_{aL}}^{\prime 3}}}};$ a _(1, P) _(aL) (t)=S _(1, P) _(aL) ″·T _(1, P) _(aL) (t)+κ_(1, P) _(aL) (t)·N _(1, P) _(aL) (t)

T _(2, P) _(aL) (t)=φ_(2, P) _(aL) (t)′/|φ_(2, P) _(aL) (t)′|;

S _(2, P) _(aL) =∫_(t) _(o) ^(t)φ_(2, P) _(aL) (u)′ du;

$\mspace{79mu} {{{{k_{2,P_{aL}}(t)} \cdot {N_{2,P_{aL}}(t)}} = \frac{T_{2,P_{aL}}}{s}};}$ ${{k_{2,P_{aL}}(t)} = {\left( \left( {\left( {D_{P_{aL}} - {\left( {\sum\limits_{k,l}{ɛ_{{rrp}_{k},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ccp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,P_{aL}}^{\prime 3}}}};$ a _(2, P) _(aL) (t)=S _(2, P) _(aL) ″·T _(2, P) _(aL) (t)+κ_(2, P) _(aL) (t)·N _(2, P) _(aL) (t)

T _(3, P) _(aL) (t)=φ_(3, P) _(aL) (t)′/|φ_(3, P) _(aL) (t)′|;

S _(3, P) _(aL) =∫_(t) _(o) ^(t)φ_(3, P) _(aL) (u)′ du;

$\mspace{79mu} {{{{k_{3,P_{aL}}(t)} \cdot {N_{3,P_{aL}}(t)}} = \frac{T_{2,P_{aL}}}{s}};}$ ${{k_{3,P_{aL}}(t)} = {\left( \left( {\left( {D_{P_{aL}} - {\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,P_{aL}}^{\prime 3}}}};$ a _(3, P) _(aL) (t)=S _(3, P) _(aL) ·T _(3, P) _(aL) (t)+κ_(3, P) _(aL) (t)·N _(3, P) _(aL) (t)

(x₁, x₂, x₃, t) is the coordinate system of the red blood cell in a neighbourhood O_(P) _(aL) of the apical Lateral and δ(x₁, x₂, x₃, t)=δ*(x₁, t)·δ*(x₂, t)·δ*(x₃, t) where δ* is the dirac function and C_(1, P) _(aL) , C_(2, P) _(aL) and C_(3, P) _(aL) are the graphs of φ_(1, P) _(aL) (t), φ_(2, P) _(aL) (t) and φ_(3, P) _(aL) (t) respectively then the mechanical parameters of the red blood cells in the region O_(P) _(aL) are calculated by the following formulae:

v _(1, P) _(aL) (t)=∫_(C) ₁ _(, P) _(aL) T _(1, P) _(aL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(1, P) _(aL) (t)=∫_(C) ₁ _(, P) _(aL) N _(1, P) _(aL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(1, P) _(aL) ^(RBC)(t)=∫_(C) ₁ _(, P) _(aL) a _(1, P) _(aL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(2, P) _(aL) (t)=∫_(C) ₂ _(, P) _(aL) T _(2, P) _(aL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(2, P) _(aL) (t)=∫_(C) ₂ _(, P) _(aL) N _(2, P) _(aL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(2, P) _(aL) ^(RBC)(t)=∫_(C) ₂ _(, P) _(aL) a _(2, P) _(aL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(3, P) _(aL) (t)=∫_(C) ₃ _(, P) _(aL) T _(3, P) _(aL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(3, P) _(aL) (t)=∫_(C) ₃ _(, P) _(aL) N _(3, P) _(aL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(3, P) _(aL) ^(RBC)(t)=∫_(C) ₃ _(, P) _(aL) a _(3, P) _(aL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

In another preferred embodiment the invention provides an analytical solution of the Navier-Stocks equations in the region O_(P) _(mL) of the mid Lateral. FIG. 23 shows a rendering of these solutions in the mathlab software.

FIG. 22 shows the mechanical parameters of blood which were induced by Q_(P) _(mL) in region O_(P) _(mL) related to apical inferior. The surface is;

F _(P) _(mL) ((y ₁ , y ₂ , y ₃))=(Σ_(k, l)ε_(rr P) _(k) ′_(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) ′_(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) ′_(, P) _(l) dt)·y ₃ ² −D _(P) _(mL)

In the region O_(P) _(mL) , let φ_(1, P) _(mL) (t), φ_(2, P) _(mL) (t) and φ_(3, P) _(mL) (t) are parameterized forms of the projections of the surface F_(P) _(mL) on xy-axis, xz-axis and yz-axis:

${{\phi_{1,P_{mL}}(t)} = \left( {t,\left( {\left( {D_{P_{mL}} - {\left( {\sum\limits_{k,l}{ɛ_{{{rr}\; p_{k}},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${{\phi_{2,P_{mL}}(t)} = \left( {t,\left( {\left( {D_{P_{mL}} - {\left( {\sum\limits_{k,l}{ɛ_{{{rr}\; p_{k}},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ccp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${\phi_{3,P_{mL}}(t)} = \left( {t,\left( {\left( {D_{P_{mL}} - {\left( {\sum\limits_{k,l}{ɛ_{{{ll}\; p_{k}},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ccp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)$

Following formulae were set;

T _(1, P) _(mL) (t)=φ_(1, P) _(mL) (t)′/|φ_(1, P) _(mL) (t)′|;

S _(1, P) _(mL) =∫_(t) _(o) ^(t)φ_(1, P) _(mL) (u)′ du;

$\mspace{79mu} {{{{k_{1,P_{mL}}(t)} \cdot {N_{1,P_{mL}}(t)}} = \frac{T_{1,P_{mL}}}{s}};}$ ${{k_{1,P_{mL}}(t)} = {\left( \left( {\left( {D_{P_{mL}} - {\left( {\sum\limits_{k,l}{ɛ_{{rrp}_{k},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,P_{mL}}^{\prime 3}}}};$ a _(1, P) _(mL) (t)=S _(1, P) _(mL) ″·T _(1, P) _(mL) (t)+κ_(1, P) _(mL) (t)·N _(1, P) _(mL) (t)

T _(2, P) _(mL) (t)=φ_(2, P) _(mL) (t)′/|φ_(2, P) _(mL) (t)′|;

S _(2, P) _(mL) =∫_(t) _(o) ^(t)φ_(2, P) _(mL) (u)′ du;

$\mspace{79mu} {{{{k_{2,P_{mL}}(t)} \cdot {N_{2,P_{mL}}(t)}} = \frac{T_{2,P_{mL}}}{s}};}$ ${{k_{2,P_{mL}}(t)} = {\left( \left( {\left( {D_{P_{mL}} - {\left( {\sum\limits_{k,l}{ɛ_{{rrp}_{k},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ccp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,P_{mL}}^{\prime 3}}}};$ a _(2, P) _(mL) (t)=S _(2, P) _(mL) ″·T _(2, P) _(mL) (t)+κ_(2, P) _(mL) (t)·N _(2, P) _(mL) (t)

T _(3, P) _(mL) (t)=φ_(3, P) _(mL) (t)′/|φ_(3, P) _(mL) (t)′|;

S _(3, P) _(mL) =∫_(t) _(o) ^(t)φ_(3, P) _(mL) (u)′ du;

$\mspace{79mu} {{{{k_{3,P_{mL}}(t)} \cdot {N_{3,P_{mL}}(t)}} = \frac{T_{2,P_{mL}}}{s}};}$ ${{k_{3,P_{mL}}(t)} = {\left( \left( {\left( {D_{P_{mL}} - {\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,P_{mL}}^{\prime 3}}}};$ a _(3, P) _(mL) (t)=S _(3, P) _(mL) ·T _(3, P) _(mL) (t)+κ_(3, P) _(mL) (t)·N _(3, P) _(mL) (t)

(x₁, x₂, x₃, t) is the coordinate system of the red blood cell in a neighbourhood O_(P) _(mL) of the mid Lateral and δ(x₁, x₂, x₃, t)=δ*(x₁, t)·δ*(x₂, t)·δ*(x₃, t) where δ* is the dirac function and C_(1, P) _(mL) , C_(2, P) _(mL) and C_(3, P) _(mL) are the graphs of φ_(1, P) _(mL) (t), φ_(2, P) _(mL) (t) and φ_(3, P) _(mL) (t) respectively then the mechanical parameters of the red blood cells in the region O_(P) _(mL) are calculated by the following formulae:

v _(1, P) _(mL) (t)=∫_(C) ₁ _(, P) _(mL) T _(1, P) _(mL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(1, P) _(mL) (t)=∫_(C) ₁ _(, P) _(mL) N _(1, P) _(mL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(1, P) _(mL) ^(RBC)(t)=∫_(C) ₁ _(, P) _(mL) a _(1, P) _(mL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(2, P) _(mL) (t)=∫_(C) ₂ _(, P) _(mL) T _(2, P) _(mL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(2, P) _(mL) (t)=∫_(C) ₂ _(, P) _(mL) N _(2, P) _(mL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(2, P) _(mL) ^(RBC)(t)=∫_(C) ₂ _(, P) _(mL) a _(2, P) _(mL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(3, P) _(mL) (t)=∫_(C) ₃ _(, P) _(mL) T _(3, P) _(mL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(3, P) _(mL) (t)=∫_(C) ₃ _(, P) _(mL) N _(3, P) _(mL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(3, P) _(mL) ^(RBC)(t)=∫_(C) ₃ _(, P) _(mL) a _(3, P) _(mL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

In another preferred embodiment the invention provides an analytical solution of the Navier-Stocks equations in the region O_(P) _(bL) of the basal Lateral. FIG. 25 shows a rendering of these solutions in the mathlab software.

FIG. 24 shows the mechanical parameters of blood which were induced by Q_(P) _(bL) in region O_(P) _(bL) related to apical inferior. The surface is;

F _(P) _(bL) ((y ₁ , y ₂ , y ₃))=(Σ_(k, l)ε_(rr P) _(k) ′_(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) ′_(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) ′_(, P) _(l) dt)·y ₃ ² −D _(P) _(bL)

In the region O_(P) _(bL) , let φ_(1, P) _(bL) (t), φ_(2, P) _(bL) (t) and φ_(3, P) _(bL) (t) are parameterized forms of the projections of the surface F_(P) _(bL) on xy-axis, xz-axis and yz-axis:

${{\phi_{1,P_{bL}}(t)} = \left( {t,\left( {\left( {D_{P_{bL}} - {\left( {\sum\limits_{k,l}{ɛ_{{{rr}\; p_{k}},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${{\phi_{2,P_{bL}}(t)} = \left( {t,\left( {\left( {D_{P_{bL}} - {\left( {\sum\limits_{k,l}{ɛ_{{{rr}\; p_{k}},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ccp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${\phi_{3,P_{bL}}(t)} = \left( {t,\left( {\left( {D_{P_{bL}} - {\left( {\sum\limits_{k,l}{ɛ_{{{ll}\; p_{k}},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ccp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)$

Following formulae were set;

T _(1, P) _(bL) (t)=φ_(1, P) _(bL) (t)′/|φ_(1, P) _(bL) (t)′|;

S _(1, P) _(bL) =∫_(t) _(o) ^(t)φ_(1, P) _(bL) (u)′ du;

$\mspace{79mu} {{{{k_{1,P_{bL}}(t)} \cdot {N_{1,P_{bL}}(t)}} = \frac{T_{1,P_{bL}}}{s}};}$ ${{k_{1,P_{bL}}(t)} = {\left( \left( {\left( {D_{P_{bL}} - {\left( {\sum\limits_{k,l}{ɛ_{{rrp}_{k},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/5_{1,P_{bL}}^{\prime 3}}}};$ a _(1, P) _(bL) (t)=S _(1, P) _(bL) ″·T _(1, P) _(bL) (t)+κ_(1, P) _(bL) (t)·N _(1, P) _(bL) (t)

T _(2, P) _(bL) (t)=φ_(2, P) _(bL) (t)′/|φ_(2, P) _(bL) (t)′|;

S _(2, P) _(bL) =∫_(t) _(o) ^(t)φ_(2, P) _(bL) (u)′ du;

$\mspace{79mu} {{{{k_{2,P_{bL}}(t)} \cdot {N_{2,P_{bL}}(t)}} = \frac{T_{2,P_{bL}}}{s}};}$ ${{k_{2,P_{bL}}(t)} = {\left( \left( {\left( {D_{P_{bL}} - {\left( {\sum\limits_{k,l}{ɛ_{{rrp}_{k},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ccp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,P_{bL}}^{\prime 3}}}};$ a _(2, P) _(bL) (t)=S _(2, P) _(bL) ″·T _(2, P) _(bL) (t)+κ_(2, P) _(bL) (t)·N _(2, P) _(bL) (t)

T _(3, P) _(bL) (t)=φ_(3, P) _(bL) (t)′/|φ_(3, P) _(bL) (t)′|;

S _(3, P) _(bL) =∫_(t) _(o) ^(t)φ_(3, P) _(bL) (u)′ du;

$\mspace{79mu} {{{{k_{3,P_{bL}}(t)} \cdot {N_{3,P_{bL}}(t)}} = \frac{T_{2,P_{bL}}}{s}};}$ ${{k_{3,P_{bL}}(t)} = {\left( \left( {\left( {D_{P_{bL}} - {\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,P_{bL}}^{\prime 3}}}};$ a _(3, P) _(bL) (t)=S _(3, P) _(bL) ·T _(3, P) _(bL) (t)+κ_(3, P) _(bL) (t)·N _(3, P) _(bL) (t)

(x₁, x₂, x₃, t) is the coordinate system of the red blood cell in a neighbourhood O_(P) _(bL) of the basal Lateral and δ(x₁, x₂, x₃, t)=δ*(x₁, t)·δ*(x₂, t)·δ*(x₃, t) where δ* is the dirac function and C_(1, P) _(bL) , C_(2, P) _(bL) and C_(3, P) _(bL) are the graphs of φ_(1, P) _(bL) (t), φ_(2, P) _(bL) (t) and φ_(3, P) _(bL) (t) respectively then the mechanical parameters of the red blood cells in the region O_(P) _(bL) are calculated by the following formulae:

v _(1, P) _(bL) (t)=∫_(C) ₁ _(, P) _(bL) T _(1, P) _(bL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(1, P) _(bL) (t)=∫_(C) ₁ _(, P) _(bL) N _(1, P) _(bL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(1, P) _(bL) ^(RBC)(t)=∫_(C) ₁ _(, P) _(bL) a _(1, P) _(bL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(2, P) _(bL) (t)=∫_(C) ₂ _(, P) _(bL) T _(2, P) _(bL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(2, P) _(bL) (t)=∫_(C) ₂ _(, P) _(bL) N _(2, P) _(bL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(2, P) _(bL) ^(RBC)(t)=∫_(C) ₂ _(, P) _(bL) a _(2, P) _(bL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(3, P) _(bL) (t)=∫_(C) ₃ _(, P) _(bL) T _(3, P) _(bL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(3, P) _(bL) (t)=∫_(C) ₃ _(, P) _(bL) N _(3, P) _(bL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(3, P) _(bL) ^(RBC)(t)=∫_(C) ₃ _(, P) _(bL) a _(3, P) _(bL) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

In an embodiment, as illustrated in FIG. 26, the invention provides mathematical signs of basal Septum, mid Septum and apical Septum to obtain good formulizations of the induced mathematical parameters of the blood.

The invention further provides geometrical modelling of the basal, mid and apical Septum as described below;

Let ε_(rr, P) _(bS) , ε_(P) _(bS) and ε_(cc, P) _(bS) be the strain components of the basal Inferior P_(bS), then

γ_(P) _(bS) ={each mayocardial sample X that ε_(rr, X)×ε_(ll, X)=ε_(rr, P) _(bS) ×ε_(ll, P) _(bS) and ε_(rr, X)×ε_(ll, X)×ε_(cc, X)=ε_(rr, P) _(bS) ×ε_(ll, P) _(bS) ×ε_(cc, P) _(bS) }

similarly for mid and apical inferior the sets are:

γ_(P) _(mS) ={each mayocardial sample X that ε_(rr, X)×ε_(ll, X)=ε_(rr, P) _(mS) ×ε_(ll, P) _(mS) and ε_(rr, X)×ε_(ll, X)×ε_(cc, X)=ε_(rr, P) _(mS) ×ε_(ll, P) _(mS) ×ε_(cc, P) _(mS) }

γ_(P) _(aS) ={each mayocardial sample X that ε_(rr, X)×ε_(ll, X)=ε_(rr, P) _(aS) ×ε_(ll, P) _(aS) and ε_(rr, X)×ε_(ll, X)×ε_(cc, X)=ε_(rr, P) _(aS) ×ε_(ll, P) _(aS) ×ε_(cc, P) _(aS) }

γ_(P) _(bS) , γ_(P) _(mS) and γ_(P) _(aS) are the myofiber bands illustrated in FIG. 2. The Q's have following values

Q _(P) _(bS) :D _(P) _(bS) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y ₃ ²

D _(P) _(bS) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y _(1, bS) ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y _(2, bS) ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y _(3, bS) ²

Where, P_(k) and P_(l) are points belonging to γ_(P) _(bS) ∩ O_(P) _(bS) and if P_(bS)=(y_(1, bS), y_(2, bS), y_(3, bS)) as Cartesian coordinate

Similarly, the Cartesian coordinates for Q's for mid and apical Inferiors are as follows;

For the mid of Septum:

Q _(P) _(mS) :D _(P) _(mS) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y ₃ ²

D _(P) _(mS) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y _(1, mS) ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y _(2, mS) ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y _(3, mS) ²

where, P_(k) and P_(l) are points belonging to γ_(P) _(mS) ∩ O_(P) _(mS) and if P_(mS)=(y_(1, mS), y_(2, mS), y_(3, mS)) as Cartesian coordinate.

For apical Anterior:

Q _(P) _(aS) :D _(P) _(aS) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y ₃ ²

D _(P) _(aS) =(Σ_(k, l)ε_(rr P) _(k) _(, P) _(l) dt)·y _(1, aS) ²+(Σ_(k, l)ε_(ll P) _(k) _(, P) _(l) dt)·y _(2, aS) ²+(Σ_(k, l)ε_(cc P) _(k) _(, P) _(l) dt)·y _(3, aS) ²

where, P_(k) and P_(l) are points belonging to γ_(P) _(aS) ∩ O_(P) _(aS) and if P_(aS)=(y_(1, aS), y_(2, aS, y) _(3, aS)) as Cartesian coordinate.

In a preferred embodiment, the invention provides an analytical solution of the Navier-Stocks equations in the region O_(P) _(aS) of the apical Septum. FIG. 30 shows a rendering of these solutions in the mathlab software.

FIG. 29, illustrates mechanical parameters of blood induced by Q_(P) _(aS) in the region O_(P) _(aS) related to apical Lateral. The surface parameters are as follows

F _(P) _(aS) ((y ₁ , y ₂ , y ₃))=(Σ_(k, l)ε_(rr P) _(k) ′_(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) ′_(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) ′_(, P) _(l) dt)·y ₃ ² −D _(P) _(aS)

In the region O_(P) _(aS) , let φ_(1, P) _(aS) (t), φ_(2, P) _(aS) (t) and φ_(3, P) _(aS) (t) are parameterized forms of the projections of the surface F_(P) _(aS) on xy-axis, xz-axis and yz-axis:

${{\phi_{1,P_{aS}}(t)} = \left( {t,\left( {\left( {D_{P_{aS}} - {\left( {\sum\limits_{k,l}{ɛ_{{{rr}\; p_{k}},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${{\phi_{2,P_{aS}}(t)} = \left( {t,\left( {\left( {D_{P_{aS}} - {\left( {\sum\limits_{k,l}{ɛ_{{{rr}\; p_{k}},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ccp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${\phi_{3,P_{aS}}(t)} = \left( {t,\left( {\left( {D_{P_{aS}} - {\left( {\sum\limits_{k,l}{ɛ_{{{ll}\; p_{k}},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ccp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)$

Following formulae were set;

T _(1, P) _(aS) (t)=φ_(1, P) _(aS) (t)′/|φ_(1, P) _(aS) (t)′|;

S _(1, P) _(aS) =∫_(t) _(o) ^(t)φ_(1, P) _(aS) (u)′ du;

$\mspace{79mu} {{{{k_{1,P_{aS}}(t)} \cdot {N_{1,P_{aS}}(t)}} = \frac{T_{1,P_{aS}}}{s}};}$ ${{k_{1,P_{aS}}(t)} = {\left( \left( {\left( {D_{P_{aS}} - {\left( {\sum\limits_{k,l}{ɛ_{{rrp}_{k},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,P_{aS}}^{\prime 3}}}};$ a _(1, P) _(aS) (t)=S _(1, P) _(aS) ″·T _(1, P) _(aS) (t)+κ_(1, P) _(aS) (t)·N _(1, P) _(aS) (t)

T _(2, P) _(aS) (t)=φ_(2, P) _(aS) (t)′/|φ_(2, P) _(aS) (t)′|;

S _(2, P) _(aS) =∫_(t) _(o) ^(t)φ_(2, P) _(aS) (u)′ du;

$\mspace{79mu} {{{{k_{2,P_{aS}}(t)} \cdot {N_{2,P_{aS}}(t)}} = \frac{T_{2,P_{aS}}}{s}};}$ ${{k_{2,P_{aS}}(t)} = {\left( \left( {\left( {D_{P_{aS}} - {\left( {\sum\limits_{k,l}{ɛ_{{rrp}_{k},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ccp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,P_{aS}}^{\prime 3}}}};$ a _(2, P) _(aS) (t)=S _(2, P) _(aS) ″·T _(2, P) _(aS) (t)+κ_(2, P) _(aS) (t)·N _(2, P) _(aS) (t)

T _(3, P) _(aS) (t)=φ_(3, P) _(aS) (t)′/|φ_(3, P) _(aS) (t)′|;

S _(3, P) _(aS) =∫_(t) _(o) ^(t)φ_(3, P) _(aS) (u)′ du;

$\mspace{79mu} {{{{k_{3,P_{aS}}(t)} \cdot {N_{3,P_{aS}}(t)}} = \frac{T_{2,P_{aS}}}{s}};}$ ${{k_{3,P_{aS}}(t)} = {\left( \left( {\left( {D_{P_{aS}} - {\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{llp}_{k},p_{l}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,P_{aS}}^{\prime 3}}}};$ a _(3, P) _(aS) (t)=S _(3, P) _(aS) ·T _(3, P) _(aS) (t)+κ_(3, P) _(aS) (t)·N _(3, P) _(aS) (t)

(x₁, x₂, x₃, t) is the coordinate system of the red blood cell in a neighbourhood O_(P) _(aS) of the apical Septum and δ(x₁, x₂, x₃, t)=δ*(x₁, t)·δ*(x₂, t)·δ*(x₃, t) where δ* is the dirac function and C_(1, P) _(aS) , C_(2, P) _(aS) and C_(3, P) _(aS) are the graphs of φ_(1, P) _(aS) (t), φ_(2, P) _(aS) (t) and φ_(3, P) _(aS) (t) respectively then the mechanical parameters of the red blood cells in the region O_(P) _(aS) are calculated by the following formulae:

v _(1, P) _(aS) (t)=∫_(C) ₁ _(, P) _(aS) T _(1, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(1, P) _(aS) (t)=∫_(C) ₁ _(, P) _(aS) N _(1, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(1, P) _(aS) ^(RBC)(t)=∫_(C) ₁ _(, P) _(aS) a _(1, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(2, P) _(aS) (t)=∫_(C) ₂ _(, P) _(aS) T _(2, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(2, P) _(aS) (t)=∫_(C) ₂ _(, P) _(aS) N _(2, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(2, P) _(aS) ^(RBC)(t)=∫_(C) ₂ _(, P) _(aS) a _(2, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(3, P) _(aS) (t)=∫_(C) ₃ _(, P) _(aS) T _(3, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(3, P) _(aS) (t)=∫_(C) ₃ _(, P) _(aS) N _(3, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(3, P) _(aS) ^(RBC)(t)=∫_(C) ₃ _(, P) _(aS) a _(3, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

In a preferred embodiment, the invention provides an analytical solution of the Navier-Stocks equations in the region O_(P) _(mS) of the mid Septum. FIG. 32 shows a rendering of these solutions in the mathlab software.

FIG. 31, illustrates mechanical parameters of blood induced by Q^(P) _(mS) in the region O_(P) _(mS) related to mid Lateral. The surface parameters are as follows

F _(P) _(mS) ((y ₁ , y ₂ , y ₃))=(Σ_(k, l)ε_(rr P) _(k) ′_(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) ′_(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) ′_(, P) _(l) dt)·y ₃ ² −D _(P) _(mS)

In the region O_(P) _(mS) , let φ_(1, P) _(mS) (t), φ_(2, P) _(mS) (t) and φ_(3, P) _(mS) (t) are parameterized forms of the projections of the surface F_(P) _(mS) on xy-axis, xz-axis and yz-axis:

${{\phi_{1,p_{mS}}(t)} = \left( {t,\left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${{\phi_{2,p_{mS}}(t)} = \left( {t,\left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${\phi_{3,p_{mS}}(t)} = \left( {t,\left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)$

Following formulae were set;

T _(1, P) _(mS) (t)=φ_(1, P) _(mS) (t)′/|φ_(1, P) _(mS) (t)′|;

S _(1, P) _(mS) =∫_(t) _(o) ^(t)φ_(1, P) _(mS) (u)′ du;

$\mspace{79mu} {{{{\kappa_{1,p_{mS}}(t)} \cdot {N_{1,p_{mS}}(t)}} = \frac{T_{1,p_{mS}}}{s}};}$ ${{\kappa_{2,p_{mS}}(t)} = {\left( \left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,p_{mS}}^{\prime \; 3}}}};$ a _(1, P) _(mS) (t)=S _(1, P) _(mS) ″·T _(1, P) _(mS) (t)+κ_(1, P) _(mS) (t)·N _(1, P) _(mS) (t)

T _(2, P) _(mS) (t)=φ_(2, P) _(mS) (t)′/|φ_(1, P) _(mS) (t)′|;

S _(2, P) _(mS) =∫_(t) _(o) ^(t)φ_(2, P) _(mS) (u)′ du;

$\mspace{79mu} {{{{\kappa_{2,p_{mS}}(t)} \cdot {N_{2,p_{mS}}(t)}} = \frac{T_{2,p_{mS}}}{s}};}$ ${{\kappa_{2,p_{mS}}(t)} = {\left( \left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,p_{mS}}^{\prime \; 3}}}};$ a _(2, P) _(mS) (t)=S _(2, P) _(mS) ″·T _(2, P) _(mS) (t)+κ_(2, P) _(mS) (t)·N _(2, P) _(mS) (t)

T _(3, P) _(mS) (t)=φ_(3, P) _(mS) (t)′/|φ_(3, P) _(mS) (t)′|;

S _(3, P) _(mS) =∫_(t) _(o) ^(t)φ_(3, P) _(mS) (u)′ du;

$\mspace{79mu} {{{{\kappa_{3,p_{mS}}(t)} \cdot {N_{3,p_{mS}}(t)}} = \frac{T_{2,p_{mS}}}{s}};}$ ${{\kappa_{3,p_{mS}}(t)} = {\left( \left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,p_{mS}}^{\prime \; 3}}}};$ a _(3, P) _(mS) (t)=S _(3, P) _(mS) ·T _(3, P) _(mS) (t)+κ_(3, P) _(mS) (t)·N _(3, P) _(mS) (t)

Following formulae were set;

T _(1, P) _(mS) (t)=φ_(1, P) _(mS) (t)′/|φ_(3, P) _(mS) (t)′|;

S _(1, P) _(mS) =∫_(t) _(o) ^(t)φ_(1, P) _(mS) (u)′ du;

$\mspace{59mu} {{{{\kappa_{1,p_{mS}}(t)} \cdot {N_{1,p_{mS}}(t)}} = \frac{T_{1,p_{mS}}}{s}};}$ ${{\kappa_{2,p_{mS}}(t)} = {\left( \left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,p_{mS}}^{\prime \; 3}}}};$ a _(1, P) _(mS) (t)=S _(1, P) _(mS) ″·T _(1, P) _(mS) (t)+κ_(1, P) _(mS) (t)·N _(1, P) _(mS) (t)

T _(2, P) _(mS) (t)=φ_(2, P) _(mS) (t)′/|φ_(2, P) _(mS) (t)′|;

S _(2, P) _(mS) =∫_(t) _(o) ^(t)φ_(2, P) _(mS) (u)′ du;

$\mspace{79mu} {{{{\kappa_{2,p_{mS}}(t)} \cdot {N_{2,p_{mS}}(t)}} = \frac{T_{2,p_{mS}}}{s}};}$ ${{\kappa_{2,p_{mS}}(t)} = {\left( \left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,p_{mS}}^{\prime \; 3}}}};$ a _(2, P) _(mS) (t)=S _(2, P) _(mS) ″·T _(2, P) _(mS) (t)+κ_(2, P) _(mS) (t)·N _(2, P) _(mS) (t)

T _(3, P) _(mS) (t)=φ_(3, P) _(mS) (t)′/|φ_(3, P) _(mS) (t)′|;

S _(3, P) _(mS) =∫_(t) _(o) ^(t)φ_(3, P) _(mS) (u)′ du;

$\mspace{85mu} {{{{\kappa_{3,p_{mS}}(t)} \cdot {N_{3,p_{mS}}(t)}} = \frac{T_{2,p_{mS}}}{s}};}$ ${{\kappa_{3,p_{mS}}(t)} = {\left( \left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,p_{mS}}^{\prime \; 3}}}};$ a _(3, P) _(mS) (t)=S _(3, P) _(mS) ·T _(3, P) _(mS) (t)+κ_(3, P) _(mS) (t)·N _(3, P) _(mS) (t)

(x₁, x₂, x₃, t) is the coordinate system of the red blood cell in a neighbourhood O_(P) _(mS) of the apical Septum and δ(x₁, x₂, x₃, t)=δ*(x₁, t)·δ*(x₂, t)·δ*(x₃, t) where δ* is the dirac function and C_(1, P) _(mS) , C_(2, P) _(mS) and C_(3, P) _(mS) are the graphs of φ_(1, P) _(mS) (t), φ_(2, P) _(mS) (t) and φ_(3, P) _(mS) (t) respectively then the mechanical parameters of the red blood cells in the region O_(P) _(mS) are calculated by the following formulae:

v _(1, P) _(mS) (t)=∫_(C) ₁ _(, P) _(mS) T _(1, P) _(mS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(1, P) _(mS) (t)=∫_(C) ₁ _(, P) _(mS) N _(1, P) _(mS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(1, P) _(mS) ^(RBC)(t)=∫_(C) ₁ _(, P) _(mS) a _(1, P) _(mS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(2, P) _(mS) (t)=∫_(C) ₂ _(, P) _(mS) T _(2, P) _(mS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(2, P) _(mS) (t)=∫_(C) ₂ _(, P) _(mS) N _(2, P) _(mS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(2, P) _(mS) ^(RBC)(t)=∫_(C) ₂ _(, P) _(mS) a _(2, P) _(mS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(3, P) _(mS) (t)=∫_(C) ₃ _(, P) _(mS) T _(3, P) _(mS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(3, P) _(mS) (t)=∫_(C) ₃ _(, P) _(mS) N _(3, P) _(mS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(3, P) _(mS) ^(RBC)(t)=∫_(C) ₃ _(, P) _(mS) a _(3, P) _(mS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

In a preferred embodiment, the invention provides an analytical solution of the Navier-Stocks equations in the region O_(P) _(aS) of the apical Septum. FIG. 30 shows a rendering of these solutions in the mathlab software.

FIG. 29, illustrates mechanical parameters of blood induced by Q_(P) _(aS) in the region O_(P) _(aS) related to apical Lateral. The surface parameters are as follows

F _(P) _(aS) ((y ₁ , y ₂ , y ₃))=(Σ_(k, l)ε_(rr P) _(k) ′_(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) ′_(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) ′_(, P) _(l) dt)·y ₃ ² −D _(P) _(aS)

In the region O_(P) _(aS) , let φ_(1, P) _(aS) (t), φ_(2, P) _(aS) (t) and φ_(3, P) _(aS) (t) are parameterized forms of the projections of the surface F_(P) _(aS) on xy-axis, xz-axis and yz-axis:

${{\phi_{1,p_{mS}}(t)} = \left( {t,\left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${{\phi_{2,p_{mS}}(t)} = \left( {t,\left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${\phi_{3,p_{mS}}(t)} = \left( {t,\left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)$

Following formulae were set;

T _(1, P) _(aS) (t)=φ_(1, P) _(aS) (t)′/|φ_(1, P) _(aS) (t)′|;

S _(1, P) _(aS) =∫_(t) _(o) ^(t)φ_(1, P) _(aS) (u)′ du;

$\mspace{76mu} {{{{\kappa_{1,p_{mS}}(t)} \cdot {N_{1,p_{mS}}(t)}} = \frac{T_{1,p_{mS}}}{s}};}$ ${{\kappa_{2,p_{mS}}(t)} = {\left( \left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,p_{mS}}^{\prime \; 3}}}};$ a _(1, P) _(aS) (t)=S _(1, P) _(aS) ·T _(1, P) _(aS) (t)+κ_(1, P) _(aS) (t)·N _(1, P) _(aS) (t)

T _(2, P) _(aS) (t)=φ_(2, P) _(aS) (t)′/|φ_(2, P) _(aS) (t)′|;

S _(2, P) _(aS) =∫_(t) _(o) ^(t)φ_(2, P) _(aS) (u)′ du;

$\mspace{79mu} {{{{\kappa_{2,p_{mS}}(t)} \cdot {N_{2,p_{mS}}(t)}} = \frac{T_{2,p_{mS}}}{s}};}$ ${{\kappa_{2,p_{mS}}(t)} = {\left( \left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,p_{mS}}^{\prime \; 3}}}};$ a _(2, P) _(aS) (t)=S _(2, P) _(aS) ″·T _(2, P) _(aS) (t)+κ_(2, P) _(aS) (t)·N _(2, P) _(aS) (t)

T _(3, P) _(aS) (t)=φ_(3, P) _(aS) (t)′/|φ_(3, P) _(aS) (t)′|;

S _(3, P) _(aS) =∫_(t) _(o) ^(t)φ_(3, P) _(aS) (u)′ du;

$\mspace{85mu} {{{{\kappa_{3,p_{mS}}(t)} \cdot {N_{3,p_{mS}}(t)}} = \frac{T_{2,p_{mS}}}{s}};}$ ${{\kappa_{3,p_{mS}}(t)} = {\left( \left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,p_{mS}}^{\prime \; 3}}}};$ a _(3, P) _(aS) (t)=S _(3, P) _(aS) ·T _(3, P) _(aS) (t)+κ_(3, P) _(aS) (t)·N _(3, P) _(aS) (t)

(x₁, x₂, x₃, t) is the coordinate system of the red blood cell in a neighbourhood O_(P) _(aS) of the apical Septum and δ(x₁, x₂, x₃, t)=δ*(x₁, t)·δ*(x₂, t)·δ*(x₃, t) where δ* is the dirac function and C_(1, P) _(aS) , C_(2, P) _(aS) and C_(3, P) _(aS) are the graphs of φ_(1, P) _(aS) (t), φ_(2, P) _(aS) (t) and φ_(3, P) _(aS) (t) respectively then the mechanical parameters of the red blood cells in the region O_(P) _(aS) are calculated by the following formulae:

v _(1, P) _(aS) (t)=∫_(C) ₁ _(, P) _(aS) T _(1, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(1, P) _(aS) (t)=∫_(C) ₁ _(, P) _(aS) N _(1, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(1, P) _(aS) ^(RBC)(t)=∫_(C) ₁ _(, P) _(aS) a _(1, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(2, P) _(aS) (t)=∫_(C) ₂ _(, P) _(aS) T _(2, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(2, P) _(aS) (t)=∫_(C) ₂ _(, P) _(aS) N _(2, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(2, P) _(aS) ^(RBC)(t)=∫_(C) ₂ _(, P) _(aS) a _(2, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(3, P) _(aS) (t)=∫_(C) ₃ _(, P) _(aS) T _(3, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(3, P) _(aS) (t)=∫_(C) ₃ _(, P) _(aS) N _(3, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(3, P) _(aS) ^(RBC)(t)=∫_(C) ₃ _(, P) _(aS) a _(3, P) _(aS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

In a preferred embodiment, the invention provides an analytical solution of the Navier-Stocks equations in the region O_(P) _(bS) of the base Septum. FIG. 34 shows a rendering of these solutions in the mathlab software.

FIG. 33, illustrates mechanical parameters of blood induced by Q_(P) _(bS) in the region O_(P) _(bS) related to mid Lateral. The surface parameters are as follows

F _(P) _(bS) ((y ₁ , y ₂ , y ₃))=(Σ_(k, l)ε_(rr P) _(k) ′_(, P) _(l) dt)·y ₁ ²+(Σ_(k, l)ε_(ll P) _(k) ′_(, P) _(l) dt)·y ₂ ²+(Σ_(k, l)ε_(cc P) _(k) ′_(, P) _(l) dt)·y ₃ ² −D _(P) _(bS)

In the region O_(P) _(bS) , let φ_(1, P) _(bS) (t), φ_(2, P) _(bS) (t) and φ_(3, P) _(bS) (t) are parameterized forms of the projections of the surface F_(P) _(bS) on xy-axis, xz-axis and yz-axis:

${{\phi_{1,p_{mS}}(t)} = \left( {t,\left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${{\phi_{2,p_{mS}}(t)} = \left( {t,\left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)};$ ${\phi_{3,p_{mS}}(t)} = \left( {t,\left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}}} \right)$

Following formulae were set;

T _(1, P) _(bS) (t)=φ_(1, P) _(bS) (t)′/|φ_(1, P) _(bS) (t)′|;

S _(1, P) _(bS) =∫_(t) _(o) ^(t)φ_(1, P) _(bS) (u)′ du;

$\mspace{79mu} {{{{\kappa_{1,p_{mS}}(t)} \cdot {N_{1,p_{mS}}(t)}} = \frac{T_{1,p_{mS}}}{s}};}$ ${{\kappa_{2,p_{mS}}(t)} = {\left( \left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,p_{mS}}^{\prime \; 3}}}};$ a _(1, P) _(bS) (t)=S _(1, P) _(bS) ″·T _(1, P) _(bS) (t)+κ_(1, P) _(bS) (t)·N _(1, P) _(bS) (t)

T _(2, P) _(bS) (t)=φ_(2, P) _(bS) (t)′/|φ_(2, P) _(bS) (t)′|;

S _(2, P) _(bS) =∫_(t) _(o) ^(t)φ_(2, P) _(bS) (u)′ du;

$\mspace{79mu} {{{{\kappa_{2,p_{mS}}(t)} \cdot {N_{2,p_{mS}}(t)}} = \frac{T_{2,p_{mS}}}{s}};}$ ${{\kappa_{2,p_{mS}}(t)} = {\left( \left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{rr}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{cc}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,p_{mS}}^{\prime \; 3}}}};$ a _(2, P) _(bS) (t)=S _(2, P) _(bS) ″·T _(2, P) _(bS) (t)+κ_(2, P) _(bS) (t)·N _(2, P) _(bS) (t)

T _(3, P) _(bS) (t)=φ_(3, P) _(bS) (t)′/|φ_(3, P) _(bS) (t)′|;

S _(3, P) _(bS) =∫_(t) _(o) ^(t)φ_(3, P) _(bS) (u)′ du;

$\mspace{85mu} {{{{\kappa_{3,p_{mS}}(t)} \cdot {N_{3,p_{mS}}(t)}} = \frac{T_{2,p_{mS}}}{s}};}$ ${{\kappa_{3,p_{mS}}(t)} = {\left( \left( {\left( {D_{p_{mS}} - {\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}\; {ɛ_{{ll}_{p_{k},p_{l}}}^{\prime}{t}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,p_{mS}}^{\prime \; 3}}}};$ a _(3, P) _(bS) (t)=S _(3, P) _(bS) ·T _(3, P) _(bS) (t)+κ_(3, P) _(bS) (t)·N _(3, P) _(bS) (t)

Following formulae were set;

T _(1, P) _(bS) (t)=φ_(1, P) _(bS) (t)′/|φ_(1, P) _(bS) (t)′|;

S _(1, P) _(bS) =∫_(t) _(o) ^(t)φ_(1, P) _(bS) (u)′ du;

$\begin{matrix} {\mspace{79mu} {{{{\kappa_{1,P_{bS}}(t)} \cdot {N_{1,P_{bS}}(t)}} = \frac{T_{1,P_{bs}}}{s}};}} \\ {{{\kappa_{1,P_{bS}}(t)} = {\left( \left( {\left( {D_{p_{bS}} - {\left( {\sum\limits_{k,l}{ɛ_{{rr}_{P_{k},P_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{1,P_{bS}}^{\,^{\prime}3}}}};} \end{matrix}$ a _(1, P) _(bS) (t)=S _(1, P) _(bS) ″·T _(1, P) _(bS) (t)+κ_(1, P) _(bS) (t)·N _(1, P) _(bS) (t)

T _(2, P) _(bS) (t)=φ_(2, P) _(bS) (t)′/|φ_(2, P) _(bS) (t)′|;

S _(2, P) _(bS) =∫_(t) _(o) ^(t)φ_(2, P) _(bS) (u)′ du;

$\begin{matrix} {\mspace{79mu} {{{{\kappa_{2,P_{bS}}(t)} \cdot {N_{2,P_{bS}}(t)}} = \frac{T_{2,P_{bS}}}{s}};}} \\ {{{\kappa_{2,P_{bS}}(t)} = {\left( \left( {\left( {D_{P_{bS}} - {\left( {\sum\limits_{k,l}{ɛ_{{rr}_{P_{k},P_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{cc}_{P_{k},P_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{2,P_{bS}}^{\,^{\prime}3}}}};} \end{matrix}$ a _(2, P) _(bS) (t)=S _(2, P) _(bS) ″·T _(2, P) _(bS) (t)+κ_(2, P) _(bS) (t)·N _(2, P) _(bS) (t)

T _(3, P) _(bS) (t)=φ_(3, P) _(bS) (t)′/|φ_(3, P) _(bS) (t)′|;

S _(3, P) _(bS) =∫_(t) _(o) ^(t)φ_(3, P) _(bS) (u)′ du;

$\begin{matrix} {\mspace{79mu} {{{{\kappa_{3,P_{bS}}(t)} \cdot {N_{3,P_{bS}}(t)}} = \frac{T_{2,P_{bS}}}{s}};}} \\ {{{\kappa_{3,P_{bS}}(t)} = {\left( \left( {\left( {D_{P_{bS}} - {\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{dt}}} \right)t^{2}}} \right)/\left( {\sum\limits_{k,l}{ɛ_{{ll}_{P_{k},P_{l}}}^{\prime}{dt}}} \right)} \right)^{\frac{1}{2}} \right) - {0/S_{3,P_{bS}}^{\,^{\prime}3}}}};} \end{matrix}$ a _(3, P) _(bS) (t)=S _(3, P) _(bS) ·T _(3, P) _(bS) (t)+κ_(3, P) _(bS) (t)·N _(3, P) _(bS) (t)

(x₁, x₂, x₃, t) is the coordinate system of the red blood cell in a neighbourhood O_(P) _(bS) of the basal Septum and δ(x₁, x₂, x₃, t)=δ*(x₁, t)·δ*(x₂, t)·δ*(x₃, t) where δ* is the dirac function and C_(1, P) _(bS) , C_(2, P) _(bS) and C_(3, P) _(bS) are the graphs of φ_(1, P) _(bS) (t), φ_(2, P) _(bS) (t) and φ_(3, P) _(bS) (t) respectively then the mechanical parameters of the red blood cells in the region O_(P) _(bS) are calculated by the following formulae:

v _(1, P) _(bS) (t)=∫_(C) ₁ _(, P) _(bS) T _(1, P) _(bS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(1, P) _(bS) (t)=∫_(C) ₁ _(, P) _(bS) N _(1, P) _(bS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(1, P) _(bS) ^(RBC)(t)=∫_(C) ₁ _(, P) _(bS) a _(1, P) _(bS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(2, P) _(bS) (t)=∫_(C) ₂ _(, P) _(bS) T _(2, P) _(bS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(2, P) _(bS) (t)=∫_(C) ₂ _(, P) _(bS) N _(2, P) _(bS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(2, P) _(bS) ^(RBC)(t)=∫_(C) ₂ _(, P) _(bS) a _(2, P) _(bS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

v _(3, P) _(bS) (t)=∫_(C) ₃ _(, P) _(bS) T _(3, P) _(bS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

n _(3, P) _(bS) (t)=∫_(C) ₃ _(, P) _(bS) N _(3, P) _(bS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

a _(3, P) _(bS) ^(RBC)(t)=∫_(C) ₃ _(, P) _(bS) a _(3, P) _(bS) (t){circle around (x)}δ(x ₁ , x ₂ , x ₃ , t)dt;

In an embodiment, the invention provides method for regionally making blood flow curve as described below;

For apical Anterior:

Setting v_(P) _(aA) (t)=(v_(1, P) _(aA) (t), v_(2, P) _(aA) (t), v_(3, P) _(aA) (t)) as field velocity vectors of the blood in region O_(P) _(aA) , field of displacements in the real time at the same region is obtained by:

r _(P) _(aA) (t, s)=(t, ∫ _(t) _(o) ^(s) v _(1, P) _(aA) (u)du, ∫ _(t) _(o) ^(s) v _(2, P) _(aA) (u)du, ∫ _(t) _(o) ^(s) v _(3, P) _(aA) (u)du)

If, algebraic form of r_(P) _(aA) is called as BFC_(P) _(aA) ((x₁, x₂, x₃, t)) then

$X_{P_{aA}} = {{Spec}\left( \frac{R\left\lbrack {x_{1},x_{2},x_{3},t} \right\rbrack}{{BFC}_{P_{aA}}\left( \left( {x_{1},x_{2},x_{3},t} \right) \right)} \right)}$

Similarly,

For mid Anterior

Setting v_(P) _(mA) (t)=(v_(1, P) _(mA) (t), v_(2, P) _(mA) (t), v_(3, P) _(mA) (t)) as field velocity vectors of the blood in region O_(P) _(mA) , field of displacements in the real time at the same region is obtained by:

r _(P) _(mA) (t, s)=(t, ∫ _(t) _(o) ^(s) v _(1, P) _(mA) (u)du, ∫ _(t) _(o) ^(s) v _(2, P) _(mA) (u)du, ∫ _(t) _(o) ^(s) v _(3, P) _(mA) (u)du)

If, algebraic form of r_(P) _(mA) is called as BFC_(P) _(mA) ((x₁, x₂, x₃, t)) then

$X_{P_{mA}} = {{Spec}\left( \frac{R\left\lbrack {x_{1},x_{2},x_{3},t} \right\rbrack}{{BFC}_{P_{mA}}\left( \left( {x_{1},x_{2},x_{3},t} \right) \right)} \right)}$

For basal Anterior

Setting v_(P) _(bA) (t)=(v_(1, P) _(bA) (t), v_(2, P) _(bA) (t), v_(3, P) _(bA) (t)) as field velocity vectors of the blood in region O_(P) _(bA) , field of displacements in the real time at the same region is obtained by:

r _(P) _(bA) (t, s)=(t, ∫ _(t) _(o) ^(s) v _(1, P) _(bA) (u)du, ∫ _(t) _(o) ^(s) v _(2, P) _(bA) (u)du, ∫ _(t) _(o) ^(s) v _(3, P) _(bA) (u)du)

If, algebraic form of r_(P) _(bA) is called as BFC_(P) _(bA) ((x₁, x₂, x₃, t)) then

$X_{P_{bA}} = {{Spec}\left( \frac{R\left\lbrack {x_{1},x_{2},x_{3},t} \right\rbrack}{{BFC}_{P_{bA}}\left( \left( {x_{1},x_{2},x_{3},t} \right) \right)} \right)}$

For the apical inferior

Setting v_(P) _(al) (t)=(v_(1, P) _(al) (t), v_(2, P) _(al) (t), v_(3, P) _(al) (t)) as field velocity vectors of the blood in region O_(P) _(al) , field of displacements in the real time at the same region is obtained by:

r _(P) _(al) (t, s)=(t, ∫ _(t) _(o) ^(s) v _(1, P) _(al) (u)du, ∫ _(t) _(o) ^(s) v _(2, P) _(al) (u)du, ∫ _(t) _(o) ^(s) v _(3, P) _(al) (u)du)

If, algebraic form of r_(P) _(al) is called as BFC_(P) _(al) ((x₁, x₂, x₃, t)) then

$X_{P_{aI}} = {{Spec}\left( \frac{R\left\lbrack {x_{1},x_{2},x_{3},t} \right\rbrack}{{BFC}_{P_{aI}}\left( \left( {x_{1},x_{2},x_{3},t} \right) \right)} \right)}$

Similarly,

For mid Inferior

Setting v_(P) _(ml) (t)=(v_(1, P) _(ml) (t), v_(2, P) _(ml) (t), v_(3, P) _(ml) (t)) as field velocity vectors of the blood in region O_(P) _(ml) , field of displacements in the real time at the same region is obtained by:

r _(P) _(ml) (t, s)=(t, ∫ _(t) _(o) ^(s) v _(1, P) _(ml) (u)du, ∫ _(t) _(o) ^(s) v _(2, P) _(ml) (u)du, ∫ _(t) _(o) ^(s) v _(3, P) _(ml) (u)du)

If, algebraic form of r_(P) _(ml) is called as BFC_(P) _(ml) ((x₁, x₂, x₃, t)) then

$X_{P_{mI}} = {{Spec}\left( \frac{R\left\lbrack {x_{1},x_{2},x_{3},t} \right\rbrack}{{BFC}_{P_{mI}}\left( \left( {x_{1},x_{2},x_{3},t} \right) \right)} \right)}$

For basal Inferior

Setting v_(P) _(bl) (t)=(v_(1, P) _(bl) (t), v_(2, P) _(bl) (t), v_(3, P) _(bl) (t)) as field velocity vectors of the blood in region O_(P) _(bl) , field of displacements in the real time at the same region is obtained by:

r _(P) _(bl) (t, s)=(t, ∫ _(t) _(o) ^(s) v _(1, P) _(bl) (u)du, ∫ _(t) _(o) ^(s) v _(2, P) _(bl) (u)du, ∫ _(t) _(o) ^(s) v _(3, P) _(bl) (u)du)

If, algebraic form of r_(P) _(bl) is called as BFC_(P) _(bl) ((x₁, x₂, x₃, t)) then

$X_{P_{bI}} = {{Spec}\left( \frac{R\left\lbrack {x_{1},x_{2},x_{3},t} \right\rbrack}{{BFC}_{P_{bI}}\left( \left( {x_{1},x_{2},x_{3},t} \right) \right)} \right)}$

For the apical Lateral

Setting v_(P) _(aL) (t)=(v_(1, P) _(aL) (t), v_(2, P) _(aL) (t), v_(3, P) _(aL) (t)) as field velocity vectors of the blood in region O_(P) _(aL) , field of displacements in the real time at the same region is obtained by:

r _(P) _(aL) (t, s)=(t, ∫ _(t) _(o) ^(s) v _(1, P) _(aL) (u)du, ∫ _(t) _(o) ^(s) v _(2, P) _(aL) (u)du, ∫ _(t) _(o) ^(s) v _(3, P) _(aL) (u)du)

If, algebraic form of r_(P) _(aL) is called as BFC_(P) _(aL) ((x₁, x₂, x₃, t)) then

$X_{P_{aL}} = {{Spec}\left( \frac{R\left\lbrack {x_{1},x_{2},x_{3},t} \right\rbrack}{{BFC}_{P_{aL}}\left( \left( {x_{1},x_{2},x_{3},t} \right) \right)} \right)}$

Similarly,

For mid Lateral

Setting v_(P) _(mL) (t)=(v_(1, P) _(mL) (t), v_(2, P) _(mL) (t), v_(3, P) _(mL) (t)) as field velocity vectors of the blood in region O_(P) _(mL) , field of displacements in the real time at the same region is obtained by:

r _(P) _(mL) (t, s)=(t, ∫ _(t) _(o) ^(s) v _(1, P) _(mL) (u)du, ∫ _(t) _(o) ^(s) v _(2, P) _(mL) (u)du, ∫ _(t) _(o) ^(s) v _(3, P) _(mL) (u)du)

If, algebraic form of r_(P) _(mL) is called as BFC_(P) _(mL) ((x₁, x₂, x₃ , t)) then

$X_{P_{mL}} = {{Spec}\left( \frac{R\left\lbrack {x_{1},x_{2},x_{3},t} \right\rbrack}{{BFC}_{P_{mL}}\left( \left( {x_{1},x_{2},x_{3},t} \right) \right)} \right)}$

For basal Lateral

Setting v_(P) _(bL) (t)=(v_(1, P) _(bL) (t), v_(2, P) _(bL) (t), v_(3, P) _(bL) (t)) as field velocity vectors of the blood in region O_(P) _(bL) , field of displacements in the real time at the same region is obtained by:

r _(P) _(bL) (t, s)=(t, ∫ _(t) _(o) ^(s) v _(1, P) _(bL) (u)du, ∫ _(t) _(o) ^(s) v _(2, P) _(bL) (u)du, ∫ _(t) _(o) ^(s) v _(3, P) _(bL) (u)du)

If, algebraic form of r_(P) _(bL) is called as BFC_(P) _(bL) ((x₁, x₂, x₃, t)) then

$X_{P_{bL}} = {{Spec}\left( \frac{R\left\lbrack {x_{1},x_{2},x_{3},t} \right\rbrack}{{BFC}_{P_{bL}}\left( \left( {x_{1},x_{2},x_{3},t} \right) \right)} \right)}$

For the apical Septum

Setting v_(P) _(aS) (t)=(v_(1, P) _(aS) (t), v_(2, P) _(aS) (t), v_(3, P) _(aS) (t)) as field velocity vectors of the blood in region O_(P) _(aS) , field of displacements in the real time at the same region is obtained by:

r _(P) _(aS) (t, s)=(t, ∫ _(t) _(o) ^(s) v _(1, P) _(aS) (u)du, ∫ _(t) _(o) ^(s) v _(2, P) _(aS) (u)du, ∫ _(t) _(o) ^(s) v _(3, P) _(aS) (u)du)

If, algebraic form of r_(P) _(aS) is called as BFC_(P) _(aS) ((x₁, x₂, x₃, t)) then

$X_{P_{aS}} = {{Spec}\left( \frac{R\left\lbrack {x_{1},x_{2},x_{3},t} \right\rbrack}{{BFC}_{P_{aS}}\left( \left( {x_{1},x_{2},x_{3},t} \right) \right)} \right)}$

Similarly,

For mid Septum

Setting v_(P) _(mS) (t)=(v_(1, P) _(mS) (t), v_(2, P) _(mS) (t), v_(3, P) _(mS) (t)) as field velocity vectors of the blood in region O_(P) _(mS) , field of displacements in the real time at the same region is obtained by:

r _(P) _(mS) (t, s)=(t, ∫ _(t) _(o) ^(s) v _(1, P) _(mS) (u)du, ∫ _(t) _(o) ^(s) v _(2, P) _(mS) (u)du, ∫ _(t) _(o) ^(s) v _(3, P) _(mS) (u)du)

If, algebraic form of r_(P) _(mS) is called as BFC_(P) _(mS) ((x₁, x₂, x₃, t)) then

$X_{P_{mS}} = {{Spec}\left( \frac{R\left\lbrack {x_{1},x_{2},x_{3},t} \right\rbrack}{{BFC}_{P_{mS}}\left( \left( {x_{1},x_{2},x_{3},t} \right) \right)} \right)}$

For basal Septum

Setting v_(P) _(bS) (t)=(v_(1, P) _(bS) (t), v_(2, P) _(bS) (t), v_(3, P) _(bS) (t)) as field velocity vectors of the blood in region O_(P) _(bS) , field of displacements in the real time at the same region is obtained by:

r _(P) _(bS) (t, s)=(t, ∫ _(t) _(o) ^(s) v _(1, P) _(bS) (u)du, ∫ _(t) _(o) ^(s) v _(2, P) _(bS) (u)du, ∫ _(t) _(o) ^(s) v _(3, P) _(bS) (u)du)

If, algebraic form of r_(P) _(bS) is called as BFC_(P) _(bS) ((x₁, x₂, x₃, t)) then

$X_{P_{bS}} = {{Spec}\left( \frac{R\left\lbrack {x_{1},x_{2},x_{3},t} \right\rbrack}{{BFC}_{P_{bS}}\left( \left( {x_{1},x_{2},x_{3},t} \right) \right)} \right)}$

The scheme of blood flow curve is as below

X_(Blood flow in LV)=X_(P) _(aA) ∪ X_(P) _(mA) ∪ X_(P) _(bA) ∪ X_(P) _(al) ∪ X_(P) _(ml) ∪ X_(P) _(bl) ∪ X_(P) _(aL) ∪ X_(P) _(mL) ∪ X_(P) _(bL) ∪ X_(P) _(aS) ∪ X_(P) _(mS) ∪ X_(P) _(bS) ; 

1. A method for solving Navier-Stokes equation of blood dynamics comprising studying blood flow curves near studies the blood flows regionally near echocardiography samples and globally inside the left ventricle.
 2. The method according to claim 1, wherein the method comprises a. Calculating mechanical parameters of blood near echocardiography samples; b. calculating the myofiber curve for echocardiography samples of step (a); c. calculating “quadratic form” for the curve of step (b) for each echocardiography samples; d. determining the blood flow curve for step (c) for each echocardiography samples and e. integrating the blood flow curves of step (d) for determining blood flow curve for left ventricle globally.
 3. The method as claimed in claim 1, wherein the mechanical parameters of blood near echocardiography samples are calculated.
 4. The method as claimed in claim 3, wherein the echocardiography samples are collected from anterior, inferior, lateral and septum.
 5. The method as claimed in claim 4, wherein anterior samples are collected from apical, mid and basal regions of anterior.
 6. The method as claimed in claim 4, wherein anterior samples are collected from apical, mid and basal regions of inferior.
 7. The method as claimed in claim 4, wherein anterior samples are collected from apical, mid and basal regions of lateral.
 8. The method as claimed in claim 4, wherein anterior samples are collected from apical, mid and basal regions of septum.
 9. A computer program product for solving Navier-Stokes equation of blood dynamics comprising: a computer readable medium having computer readable program code embodied therein, the computer readable program code comprising: computer readable program code configured to determine studying blood flow curves near studies the blood flows regionally near echocardiography samples and globally inside the left ventricle.
 10. A computer program product according to claim 9, wherein the mechanical parameters of blood near echocardiography samples are calculated.
 11. A computer program product according to claim 10, wherein the echocardiography samples are collected from anterior, inferior, lateral and septum.
 12. A computer program product according to claim 11, wherein anterior samples are collected from apical, mid and basal regions of anterior.
 13. A computer program product according to claim 11, wherein anterior samples are collected from apical, mid and basal regions of inferior.
 14. A computer program product according to claim 11, wherein anterior samples are collected from apical, mid and basal regions of lateral.
 15. A computer program product according to claim 11, wherein anterior samples are collected from apical, mid and basal regions of septum.
 16. An echocardiography system for solving Navier-Stokes equation of blood dynamics comprising studying blood flow curves near studies the blood flows regionally near echocardiography samples and globally inside the left ventricle.
 17. The echocardiography system as claimed in claim 16, wherein the mechanical parameters of blood near echocardiography samples are calculated.
 18. The echocardiography system as claimed in claim 17, wherein the echocardiography samples are collected from anterior, inferior, lateral and septum and wherein anterior samples are collected from apical, mid and basal regions of septum.
 19. The echocardiography system as claimed in claim 18, wherein anterior samples are collected from apical, mid and basal regions of anterior and lateral.
 20. The echocardiography system as claimed in claim 18, wherein anterior samples are collected from apical, mid and basal regions of inferior. 